Hyperspectral, fluorescence, and laser mapping imaging with fixed pattern noise cancellation

ABSTRACT

Hyperspectral, fluorescence, and laser mapping imaging with reduced fixed pattern noise is disclosed. A method includes actuating an emitter to emit a plurality of pulses of electromagnetic radiation and sensing reflected electromagnetic radiation resulting from the plurality of pulses of electromagnetic radiation with a pixel array of an image sensor. The method includes reducing fixed pattern noise in an exposure frame by subtracting a reference frame from the exposure frame. The method is such that at least a portion of the pulses of electromagnetic radiation emitted by the emitter comprises one or more of: electromagnetic radiation having a wavelength from about 513 nm to about 545 nm, from about 565 nm to about 585 nm, from about 900 nm to about 1000 nm, an excitation wavelength of electromagnetic radiation that causes a reagent to fluoresce, or a laser mapping pattern.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a continuation of U.S. patent application Ser. No.16/735,943, filed Jan. 7, 2020, which claims the benefit of U.S.Provisional Patent Application No. 62/864,218, filed Jun. 20, 2019,titled “HYPERSPECTRAL AND FLUORESCENCE IMAGING WITH FIXED PATTERN NOISECANCELLATION,” which are incorporated herein by reference in itsentirety, including but not limited to those portions that specificallyappear hereinafter, the incorporation by reference being made with thefollowing exception: In the event that any portion of theabove-referenced applications are inconsistent with this application,this application supersedes the above-referenced applications.

TECHNICAL FIELD

This disclosure is directed to digital imaging and is particularlydirected to hyperspectral imaging, fluorescence imaging, and/or lasermapping imaging in a light deficient environment.

BACKGROUND

Advances in technology have provided advances in imaging capabilitiesfor medical use. An endoscope may be used to look inside a body andexamine the interior of an organ or cavity of the body. Endoscopes areused for investigating a patient's symptoms, confirming a diagnosis, orproviding medical treatment. A medical endoscope may be used for viewinga variety of body systems and parts such as the gastrointestinal tract,the respiratory tract, the urinary tract, the abdominal cavity, and soforth. Endoscopes may further be used for surgical procedures such asplastic surgery procedures, procedures performed on joints or bones,procedures performed on the neurological system, procedures performedwithin the abdominal cavity, and so forth.

In some instances of endoscopic imaging, it may be beneficial ornecessary to view a space in color. A digital color image includes atleast three layers, or “color channels,” that cumulatively form an imagewith a range of hues. Each of the color channels measures the intensityand chrominance of light for a spectral band. Commonly, a digital colorimage includes a color channel for red, green, and blue spectral bandsof light (this may be referred to as a Red Green Blue or RGB image).Each of the red, green, and blue color channels include brightnessinformation for the red, green, or blue spectral band of light. Thebrightness information for the separate red, green, and blue layers arecombined to create the color image. Because a color image is made up ofseparate layers, a conventional digital camera image sensor includes acolor filter array that permits red, green, and blue visible lightwavelengths to hit selected pixel sensors. Each individual pixel sensorelement is made sensitive to red, green, or blue wavelengths and willonly return image data for that wavelength. The image data from thetotal array of pixel sensors is combined to generate the RGB image. Theat least three distinct types of pixel sensors consume significantphysical space such that the complete pixel array cannot fit in thesmall distal end of an endoscope.

Because a traditional image sensor cannot fit in the distal end of anendoscope, the image sensor is traditionally located in a handpiece unitof an endoscope that is held by an endoscope operator and is not placedwithin the body cavity. In such an endoscope, light is transmitted alongthe length of the endoscope from the handpiece unit to the distal end ofthe endoscope. This configuration has significant limitations.Endoscopes with this configuration are delicate and can be easilymisaligned or damaged when bumped or impacted during regular use. Thiscan significantly degrade the quality of the images and necessitate thatthe endoscope be frequently repaired or replaced.

The traditional endoscope with the image sensor placed in the handpieceunit is further limited to capturing only color images. However, in someimplementations, it may be desirable to capture images withfluorescence, hyperspectral, and/or laser mapping data in addition tocolor image data. Fluorescence imaging captures the emission of light bya substance that has absorbed electromagnetic radiation and “glows” asit emits a relaxation wavelength. Hyperspectral imaging can be used toidentify different materials, biological processes, and chemicalprocesses by emitting different partitions of electromagnetic radiationand assessing the spectral responses of materials. Laser mapping imagingcan capture the surface shape of objects and landscapes and measuredistances between objects within a scene. Laser mapping imaging mayfurther encompass tool tracking wherein the distances and/or dimensionsof tools within a scene can be tracked relative to each other, relativeto an imaging device, and/or relative to structures within the scene. Insome implementations, it may be desirable to use one or more offluorescence imaging, hyperspectral imaging, and/or laser mappingimaging in combination when imaging a scene.

However, applications of fluorescence, hyperspectral, and laser mappingtechnology known in the art typically require highly specializedequipment that may not be useful for multiple applications. Further,such technologies provides a limited view of an environment andtypically must be used in conjunction with multiple separate systems andmultiple separate image sensors that are made sensitive to specificbands of electromagnetic radiation. It is therefore desirable to developan imaging system that can be used in a space constrained environment togenerate fluorescence, hyperspectral, and or laser mapping imaging data.

In light of the foregoing, described herein are systems, methods, anddevices for fluorescence, hyperspectral, and laser mapping imaging in alight deficient environment. Such systems, methods, and devices mayprovide multiple datasets for identifying critical structures in a bodyand providing precise and valuable information about a body cavity.

BRIEF DESCRIPTION OF THE DRAWINGS

Non-limiting and non-exhaustive implementations of the disclosure aredescribed with reference to the following figures, wherein likereference numerals refer to like parts throughout the various viewsunless otherwise specified. Advantages of the disclosure will becomebetter understood with regard to the following description andaccompanying drawings where:

FIG. 1 is a schematic view of a system for digital imaging in a lightdeficient environment with a paired emitter and pixel array;

FIG. 2 is a system for providing illumination to a light deficientenvironment for endoscopic imaging;

FIG. 2A is a schematic diagram of complementary system hardware;

FIGS. 3A to 3D are illustrations of the operational cycles of a sensorused to construct an exposure frame;

FIG. 4A is a graphical representation of the operation of an embodimentof an electromagnetic emitter;

FIG. 4B is a graphical representation of varying the duration andmagnitude of the emitted electromagnetic pulse to provide exposurecontrol;

FIG. 5 is a graphical representation of an embodiment of the disclosurecombining the operational cycles of a sensor, the electromagneticemitter, and the emitted electromagnetic pulses of FIGS. 3A-4B, whichdemonstrate the imaging system during operation;

FIG. 6A is a schematic diagram of a process for recording a video withfull spectrum light over a period of time from t(0) to t(1);

FIG. 6B is a schematic diagram of a process for recording a video bypulsing portioned spectrum light over a period of time from t(0) tot(1);

FIGS. 7A-7E illustrate schematic views of the processes over an intervalof time for recording a frame of video for both full spectrum light andpartitioned spectrum light;

FIG. 8A illustrates a traditional image sensor with optical black pixelsdisposed around a recording area of active pixels;

FIG. 8B illustrates an embodiment of a minimal area image sensor;

FIG. 9 is a readout sequence of an embodiment of an image sensor;

FIG. 10 is a readout sequence of an embodiment of a minimal area imagesensor;

FIG. 11 is a graphical representation of a simple exponential smoothingpixel offset estimation with small and large values for w;

FIG. 12 is a graphical representation of a modulation of the simpleexponential smoothing index after a gain change;

FIG. 13 is a schematic diagram of a process flow for cancellation offixed pattern noise;

FIG. 14 is a schematic diagram of a process flow to be implemented by acontroller and/or monochrome image signal processor for generating avideo stream having RGB images with specialty data overlaid thereon;

FIG. 15 is a schematic diagram of method and hardware schematics for usewith a partitioned light system;

FIG. 16 is a schematic diagram of a process flow for performingcorrections and adjustments on digital image data;

FIG. 17 is a schematic diagram of a pattern reconstruction process forgenerating an RGB image with specialty data overlaid thereon by pulsingpartitioned spectrums of light;

FIGS. 18A-18C illustrate a light source having a plurality of emitters;

FIG. 19 illustrates a single optical fiber outputting via a diffuser atan output to illuminate a scene in a light deficient environment;

FIG. 20 illustrates a portion of the electromagnetic spectrum dividedinto a plurality of different sub-spectrums which may be emitted byemitters of a light source in accordance with the principles andteachings of the disclosure;

FIG. 21 is a schematic diagram illustrating a timing sequence foremission and readout for generating an image frame comprising aplurality of exposure frames resulting from differing partitions ofpulsed light;

FIG. 22 illustrates an imaging system including a single cut filter forfiltering wavelengths of electromagnetic radiation;

FIG. 23 illustrates an imaging system comprising a multiple cut filterfor filtering wavelengths of electromagnetic radiation;

FIG. 24 illustrates an example laser mapping pattern that may be pulsedby an imaging system;

FIGS. 25A and 25B illustrate an implementation having a plurality ofpixel arrays for producing a three-dimensional image in accordance withthe principles and teachings of the disclosure;

FIGS. 26A and 26B illustrate a perspective view and a side view,respectively, of an implementation of an imaging sensor built on aplurality of substrates, wherein a plurality of pixel columns formingthe pixel array are located on the first substrate and a plurality ofcircuit columns are located on a second substrate and showing anelectrical connection and communication between one column of pixels toits associated or corresponding column of circuitry; and

FIGS. 27A and 27B illustrate a perspective view and a side view,respectively, of an implementation of an imaging sensor having aplurality of pixel arrays for producing a three-dimensional image,wherein the plurality of pixel arrays and the image sensor are built ona plurality of substrates.

DETAILED DESCRIPTION

Disclosed herein are systems, methods, and devices for digital imagingthat may be primarily suited to medical applications such as medicalendoscopic imaging. An embodiment of the disclosure is an endoscopicsystem for fluorescence, hyperspectral, and/or laser mapping imaging ofa light deficient environment.

An embodiment of the disclosure is an endoscopic imaging system with aCMOS (Complementary Metal Oxide Semiconductor) image sensor. CMOS imagesensors suffer from multiple sources of image noise. Image noise israndom variation of brightness or color information and can be caused byelectronic noise. Image noise is generally undesirable and can degradethe quality of an image. Image noise can range from almost imperceptiblespecks on a digital image taken in good lighting conditions, to opticalimages that are almost entirely noise, from which only a small amount ofinformation can be derived by sophisticated image processing. The amountof noise in an image generated by a CMOS image sensor is dependent on awide range of physical conditions. Pure Poisson or Gaussian temporalnoise with no coherent components such as photon shot noise or sourcefollower read noise can look natural within a video stream. Other formsof perceivable noise will degrade image quality and may be unacceptablein some implementations.

One form of noise that can cause issues with CMOS image sensors isspatial noise (SN). Spatial noise has at least two sources, includingpixel fixed pattern noise (pixel FPN) and column fixed pattern noise(column FPN). Pixel fixed pattern noise is mostly due to variations inphotodiode leakage current (may be referred to as “dark signal”) frompixel to pixel. This source can be dependent on junction temperature andexposure time. Column fixed pattern noise is a consequence of thereadout architecture in which pixels from within the same column arechanneled through common analog readout elements. In manyimplementations, it is desirable to cancel out image noise andparticularly to cancel out fixed pattern noise. In light of theforegoing, disclosed herein are systems, methods, and devices forimaging in a light deficient environment and cancelling fixed patternnoise in resulting images.

Conventional endoscopes are designed such that the image sensor isplaced at a proximal end of the device within a handpiece unit. Thisconfiguration requires that incident light travel the length of theendoscope by way of precisely coupled optical elements. The preciseoptical elements can easily be misaligned during regular use, and thiscan lead to image distortion or image loss. Embodiments of thedisclosure place an image sensor within a distal end of the endoscopeitself. This provides greater optical simplicity when compared withimplementations known in the art. However, an acceptable solution tothis approach is by no means trivial and introduces its own set ofengineering challenges, not least of which that the image sensor mustfit within a highly constrained area. Disclosed herein are systems,methods, and devices for digital imaging in a light deficientenvironment that employ minimal area image sensors and can be configuredfor hyperspectral, fluorescence, and/or laser mapping and color imaging.

In some instances, it is desirable to generate endoscopic imaging withmultiple data types or multiple images overlaid on one another. Forexample, it may be desirable to generate a color (“RGB”) image thatfurther includes hyperspectral, fluorescence, and/or laser mappingimaging data overlaid on the RGB image. An overlaid image of this naturemay enable a medical practitioner or computer program to identify highlyaccurate dimensions and three-dimensional topologies of critical bodystructures and further identify distances between tools and otherstructures within the light deficient environment based on the lasermapping data. Historically, this would require the use of multiplesensor systems including an image sensor for color imaging and one ormore additional image sensors for hyperspectral, fluorescence, or lasermapping imaging. In such systems, the multiple image sensors would havemultiple types of pixel sensors that are each sensitive to distinctranges of electromagnetic radiation. In systems known in the art, thisincludes the three separate types of pixel sensors for generating an RGBcolor image along with additional sensors and systems for generating thehyperspectral, fluorescence, and laser mapping data. These multipledifferent sensors consume a prohibitively large physical space andcannot be located at a distal tip of the endoscope. In systems known inthe art, the camera or cameras are not placed at the distal tip of theendoscope and are instead placed in an endoscope handpiece or roboticunit. This introduces numerous disadvantages and causes the endoscope tobe very delicate. The delicate endoscope may be damaged and imagequality may be degraded when the endoscope is bumped or impacted duringuse. Considering the foregoing, disclosed herein are systems, methods,and devices for endoscopic imaging in a light deficient environment. Thesystems, methods, and devices disclosed herein provide means foremploying multiple imaging techniques in a single imaging session whilepermitting one or more image sensors to be disposed in a distal tip ofthe endoscope.

The fluorescence imaging techniques discussed herein can be used incombination with one or more fluorescent reagents or dyes. The locationof a reagent can be identified by emitting an excitation wavelength ofelectromagnetic radiation that causes the reagent to fluoresce. Therelaxation wavelength emitted by the reagent can be read by an imagesensor to identify the location of the reagent within a scene. Dependingon the type of reagent that is used, the location of the reagent mayfurther indicate the location of critical structures such as certaintypes of tissue, cancerous cells versus non-cancerous cells, and soforth.

The hyperspectral imaging techniques discussed herein can be used to“see through” layers of tissue in the foreground of a scene to identifyspecific types of tissue and/or specific biological or chemicalprocesses. Hyperspectral imaging can be used in the medical context toquantitatively track the process of a disease and to determine tissuepathology. Additionally, hyperspectral imaging can be used to identifycritical structures such as nervous tissue, muscle tissue, cancerouscells, and so forth. In an embodiment, partitions of electromagneticradiation are pulsed, and data is gathered regarding the spectralresponses of different types of tissue in response to the partitions ofelectromagnetic radiation. A datastore of spectral responses can begenerated and analyzed to assess a scene and predict which tissues arepresent within the scene based on the sensed spectral responses.

The laser mapping imaging techniques discussed herein can be assessed togenerate a three-dimensional landscape map of a scene and to calculatedistances between objects within the scene. The laser mapping data canbe used in conjunction with fluorescence imaging and/or hyperspectralimaging to calculate the precise location and dimensions of criticalstructures. For example, the location and boundaries of a criticalstructure may be identified with the fluorescence and/or hyperspectralimaging. The precise measurements for the location of the criticalstructure, the dimensions of the critical structure, and the distancefrom the critical structure to other objects can then be calculatedbased on the laser mapping data.

Hyperspectral Imaging

In an embodiment, the systems, methods, and devices disclosed hereinprovide means for generating hyperspectral imaging data in a lightdeficient environment. Spectral imaging uses multiple bands across theelectromagnetic spectrum. This is different from conventional camerasthat only capture light across the three wavelengths based in thevisible spectrum that are discernable by the human eye, including thered, green, and blue wavelengths to generate an RGB image. Spectralimaging may use any wavelength bands in the electromagnetic spectrum,including infrared wavelengths, the visible spectrum, the ultravioletspectrum, x-ray wavelengths, or any suitable combination of variouswavelength bands.

Hyperspectral imaging was originally developed for applications inmining and geology. Unlike a normal camera image that provides limitedinformation to the human eye, hyperspectral imaging can identifyspecific minerals based on the spectral signatures of the differentminerals. Hyperspectral imaging can be useful even when captured inaerial images and can provide information about, for example, oil or gasleakages from pipelines or natural wells and their effects on nearbyvegetation. This information is collected based on the spectralsignatures of certain materials, objects, or processes that may beidentified by hyperspectral imaging.

Hyperspectral imaging includes spectroscopy and digital photography. Inan embodiment of hyperspectral imaging, a complete spectrum or somespectral information is collected at every pixel in an image plane. Thegoal of hyperspectral imaging may vary for different applications. Inone application, the goal of hyperspectral imaging is to obtain theentire electromagnetic spectrum of each pixel in an image scene. Thismay enable certain objects to be found that might otherwise not beidentifiable under the visible light wavelength bands. This may enablecertain materials or tissues to be identified with precision when thosematerials or tissues might not be identifiable under the visible lightwavelength bands. Further, this may enable certain processes to bedetected by capturing an image across all wavelengths of theelectromagnetic spectrum.

In an embodiment of the disclosure, an endoscope system illuminates asource and pulses electromagnetic radiation for spectral orhyperspectral imaging. Spectral imaging uses multiple bands across theelectromagnetic spectrum. This is different from conventional camerasthat only capture light across the three wavelengths based in thevisible spectrum that are discernable by the human eye, including thered, green, and blue wavelengths to generate an RGB image. Spectralimaging may use any wavelength bands in the electromagnetic spectrum,including infrared wavelengths, the visible spectrum, the ultravioletspectrum, x-ray wavelengths, or any suitable combination of variouswavelength bands. Spectral imaging may overlay imaging generated basedon non-visible bands (e.g., infrared) on top of imaging based on visiblebands (e.g. a standard RGB image) to provide additional information thatis easily discernable by a person or computer algorithm.

Hyperspectral imaging enables numerous advantages over conventionalimaging. The information obtained by hyperspectral imaging enablesmedical practitioners and/or computer-implemented programs to preciselyidentify certain tissues or conditions that may not be possible toidentify with RGB imaging. Additionally, hyperspectral imaging may beused during medical procedures to provide image-guided surgery thatenables a medical practitioner to, for example, view tissues locatedbehind certain tissues or fluids, identify atypical cancerous cells incontrast with typical healthy cells, identify certain tissues orconditions, identify critical structures, and so forth. Hyperspectralimaging provides specialized diagnostic information about tissuephysiology, morphology, and composition that cannot be generated withconventional imaging.

Hyperspectral imaging may provide particular advantages overconventional imaging in medical applications. The information obtainedby hyperspectral imaging can enable medical practitioners and/orcomputer-implemented programs to precisely identify certain tissues orconditions that may lead to diagnoses that may not be possible or may beless accurate if using conventional imaging such as RGB imaging.Additionally, hyperspectral imaging may be used during medicalprocedures to provide image-guided surgery that may enable a medicalpractitioner to, for example, view tissues located behind certaintissues or fluids, identify atypical cancerous cells in contrast withtypical healthy cells, identify certain tissues or conditions, identifycritical structures and so forth. Hyperspectral imaging may providespecialized diagnostic information about tissue physiology, morphology,and composition that cannot be generated with conventional imaging.

Endoscopic hyperspectral imaging may present advantages overconventional imaging in various applications and implementations of thedisclosure. In medical implementations, endoscopic hyperspectral imagingmay permit a practitioner or computer-implemented program to discern,for example, nervous tissue, muscle tissue, various vessels, thedirection of blood flow, and so forth. Hyperspectral imaging may enableatypical cancerous tissue to be precisely differentiated from typicalhealthy tissue and may therefore enable a practitioner orcomputer-implemented program to discern the boundary of a canceroustumor during an operation or investigative imaging. Additionally,hyperspectral imaging in a light deficient environment as disclosedherein may be combined with the use of a reagent or dye to enablefurther differentiation between certain tissues or substances. In suchan embodiment, a reagent or dye may be fluoresced by a specificwavelength band in the electromagnetic spectrum and therefore provideinformation specific to the purpose of that reagent or dye. The systems,methods, and devices disclosed herein may enable any number ofwavelength bands to be pulsed such that one or more reagents or dyes maybe fluoresced at different times, and further so that one or morepartitions of electromagnetic radiation may be pulsed for hyperspectralimaging in the same imaging session. In certain implementations, thisenables the identification or investigation of a number of medicalconditions during a single imaging procedure.

Fluorescence Imaging

The systems, methods, and devices disclosed herein provide means forgenerating fluorescence imaging data in a light deficient environment.The fluorescence imaging data may be used to identify certain materials,tissues, components, or processes within a body cavity or other lightdeficient environment. In certain embodiments, fluorescence imaging isprovided to a medical practitioner or computer-implemented program toenable the identification of certain structures or tissues within abody. Such fluorescence imaging data may be overlaid on black-and-whiteor RGB images to provide additional information and context.

Fluorescence is the emission of light by a substance that has absorbedlight or other electromagnetic radiation. Certain fluorescent materialsmay “glow” or emit a distinct color that is visible to the human eyewhen the fluorescent material is subjected to ultraviolet light or otherwavelengths of electromagnetic radiation. Certain fluorescent materialswill cease to glow nearly immediately when the radiation source stops.

Fluorescence occurs when an orbital electron of a molecule, atom, ornanostructure is excited by light or other electromagnetic radiation,and then relaxes to its ground state by emitting a photon from theexcited state. The specific frequencies of electromagnetic radiationthat excite the orbital electron, or are emitted by the photon duringrelaxation, are dependent on the particular atom, molecule, ornanostructure. In most cases, the light emitted by the substance has alonger wavelength, and therefore lower energy, than the radiation thatwas absorbed by the substance. However, when the absorbedelectromagnetic radiation is intense, it is possible for one electron toabsorb two photons. This two-photon absorption can lead to emission ofradiation having a shorter wavelength, and therefore higher energy, thanthe absorbed radiation. Additionally, the emitted radiation may also bethe same wavelength as the absorbed radiation.

Fluorescence imaging has numerous practical applications, includingmineralogy, gemology, medicine, spectroscopy for chemical sensors,detecting biological processes or signals, and so forth. Fluorescencemay particularly be used in biochemistry and medicine as anon-destructive means for tracking or analyzing biological molecules.The biological molecules, including certain tissues or structures, maybe tracked by analyzing the fluorescent emission of the biologicalmolecules after being excited by a certain wavelength of electromagneticradiation. However, relatively few cellular components are naturallyfluorescent. In certain implementations, it may be desirable tovisualize a certain tissue, structure, chemical process, or biologicalprocess that is not intrinsically fluorescent. In such animplementation, the body may be administered a dye or reagent that mayinclude a molecule, protein, or quantum dot having fluorescentproperties. The reagent or dye may then fluoresce after being excited bya certain wavelength of electromagnetic radiation. Different reagents ordyes may include different molecules, proteins, and/or quantum dots thatwill fluoresce at particular wavelengths of electromagnetic radiation.Thus, it may be necessary to excite the reagent or dye with aspecialized band of electromagnetic radiation to achieve fluorescenceand identify the desired tissue, structure, or process in the body.

Fluorescence imaging may provide valuable information in the medicalfield that may be used for diagnostic purposes and/or may be visualizedin real-time during a medical procedure. Specialized reagents or dyesmay be administered to a body to fluoresce certain tissues, structures,chemical processes, or biological processes. The fluorescence of thereagent or dye may highlight body structures such as blood vessels,nerves, particular organs, and so forth. Additionally, the fluorescenceof the reagent or dye may highlight conditions or diseases such ascancerous cells or cells experiencing a certain biological or chemicalprocess that may be associated with a condition or disease. Thefluorescence imaging may be used in real-time by a medical practitioneror computer program for differentiating between, for example, cancerousand non-cancerous cells during a surgical tumor extraction. Thefluorescence imaging may further be used as a non-destructive means fortracking and visualizing over time a condition in the body that wouldotherwise not be visible by the human eye or distinguishable in an RGBimage.

The systems, methods, and devices for generating fluorescence imagingdata may be used in coordination with reagents or dyes. Some reagents ordyes are known to attach to certain types of tissues and fluoresce atspecific wavelengths of the electromagnetic spectrum. In animplementation, a reagent or dye is administered to a patient that isconfigured to fluoresce when activated by certain wavelengths of light.The endoscopic imaging system disclosed herein is used to excite andfluoresce the reagent or dye. The fluorescence of the reagent or dye iscaptured by the endoscopic imaging system to aid in the identificationof tissues or structures in the body cavity. In an implementation, apatient is administered a plurality of reagents or dyes that are eachconfigured to fluoresce at different wavelengths and/or provide anindication of different structures, tissues, chemical reactions,biological processes, and so forth. In such an implementation, theendoscopic imaging system emits each of the applicable wavelengths tofluoresce each of the applicable reagents or dyes. This may negate theneed to perform individual imaging procedures for each of the pluralityof reagents or dyes.

Imaging reagents can enhance imaging capabilities in pharmaceutical,medical, biotechnology, diagnostic, and medical procedure industries.Many imaging techniques such as X-ray, computer tomography (CT),ultrasound, magnetic resonance imaging (MRI), and nuclear medicine,mainly analyze anatomy and morphology and are unable to detect changesat the molecular level. Fluorescent reagents, dyes, and probes,including quantum dot nanoparticles and fluorescent proteins, assistmedical imaging technologies by providing additional information aboutcertain tissues, structures, chemical processes, and/or biologicalprocesses that are present within the imaging region. Imaging usingfluorescent reagents enables cell tracking and/or the tracking ofcertain molecular biomarkers. Fluorescent reagents may be applied forimaging cancer, infection, inflammation, stem cell biology, and others.Numerous fluorescent reagents and dyes are being developed and appliedfor visualizing and tracking biological processes in a non-destructivemanner. Such fluorescent reagents may be excited by a certain wavelengthor band of wavelengths of electromagnetic radiation. Similarly, thosefluorescent reagents may emit relaxation energy at a certain wavelengthor band of wavelengths when fluorescing, and the emitted relaxationenergy may be read by a sensor to determine the location and/orboundaries of the reagent or dye.

In an embodiment of the disclosure, an endoscopic imaging system pulseselectromagnetic radiation for exciting an electron in a fluorescentreagent or dye. The endoscopic imaging system may pulse multipledifferent wavelengths of electromagnetic radiation for fluorescingmultiple different reagents or dyes during a single imaging session. Theendoscope includes an image sensor that is sensitive to the relaxationwavelength(s) of the one or more reagents or dyes. The imaging datagenerated by the image sensor can be used to identify a location andboundary of the one or more reagents or dyes. The endoscope system mayfurther pulse electromagnetic radiation in red, green, and blue bands ofvisible light such that the fluorescence imaging can be overlaid on anRGB video stream.

Laser Mapping Imaging

In an embodiment, the systems, methods, and devices disclosed hereinprovide means for generating laser mapping data with an endoscopicimaging system. Laser mapping data can be used to determine precisemeasurements and topographical outlines of a scene. In oneimplementation, laser mapping data is used to determine precisemeasurements between, for example, structures or organs in a bodycavity, devices or tools in the body cavity, and/or critical structuresin the body cavity. As discussed herein, the term “laser mapping” mayencompass technologies referred to as laser mapping, laser scanning,topographical scanning, three-dimensional scanning, laser tracking, tooltracking, and others. A laser mapping exposure frame as discussed hereinmay include topographical data for a scene, dimensions between objectsor structures within a scene, dimensions or distances for tools orobjects within a scene, and so forth.

Laser mapping generally includes the controlled deflection of laserbeams. Within the field of three-dimensional object scanning, lasermapping combines controlled steering of laser beams with a laserrangefinder. By taking a distance measurement at every direction, thelaser rangefinder can rapidly capture the surface shape of objects,tools, and landscapes. Construction of a full three-dimensional topologymay include combining multiple surface models that are obtained fromdifferent viewing angles. Various measurement systems and methods existin the art for applications in archaeology, geography, atmosphericphysics, autonomous vehicles, and others. One such system includes lightdetection and ranging (LIDAR), which is a three-dimensional lasermapping system. LIDAR has been applied in navigation systems such asairplanes or satellites to determine position and orientation of asensor in combination with other systems and sensors. LIDAR uses activesensors to illuminate an object and detect energy that is reflected offthe object and back to a sensor.

As discussed herein, the term “laser mapping” includes laser tracking.Laser tracking, or the use of lasers for tool tracking, measures objectsby determining the positions of optical targets held against thoseobjects. Laser trackers can be accurate to the order of 0.025 mm over adistance of several meters. In an embodiment, an endoscopic imagingsystem pulses light for use in conjunction with a laser tracking systemsuch that the position or tools within a scene can be tracked andmeasured. In such an embodiment, the endoscopic imaging system may pulsea laser tracking pattern on a tool, object, or other structure within ascene being imaged by the endoscopic imaging system. A target may beplaced on the tool, object, or other structure within the scene.Measurements between the endoscopic imaging system and the target can betriggered and taken at selected points such that the position of thetarget (and the tool, object, or other structure to which the target isaffixed) can be tracked by the endoscopic imaging system.

Pulsed Imaging

Some implementations of the disclosure include aspects of a combinedsensor and system design that allows for high definition imaging withreduced pixel counts in a controlled illumination environment. This isaccomplished with frame-by-frame pulsing of a single-color wavelengthand switching or alternating each frame between a single, differentcolor wavelength using a controlled light source in conjunction withhigh frame capture rates and a specially designed correspondingmonochromatic sensor. The pixels may be color agnostic such that eachpixel generates data for each pulse of electromagnetic radiation,including pulses for red, green, and blue visible light wavelengthsalong with other wavelengths used for laser mapping imaging.

For the purposes of promoting an understanding of the principles inaccordance with the disclosure, reference will now be made to theembodiments illustrated in the drawings and specific language will beused to describe the same. It will nevertheless be understood that nolimitation of the scope of the disclosure is thereby intended. Anyalterations and further modifications of the inventive featuresillustrated herein, and any additional applications of the principles ofthe disclosure as illustrated herein, which would normally occur to oneskilled in the relevant art and having possession of this disclosure,are to be considered within the scope of the disclosure claimed.

Before the structure, systems and methods for producing an image in alight deficient environment are disclosed and described, it is to beunderstood that this disclosure is not limited to the particularstructures, configurations, process steps, and materials disclosedherein as such structures, configurations, process steps, and materialsmay vary somewhat. It is also to be understood that the terminologyemployed herein is used for the purpose of describing particularembodiments only and is not intended to be limiting since the scope ofthe disclosure will be limited only by the appended claims andequivalents thereof.

In describing and claiming the subject matter of the disclosure, thefollowing terminology will be used in accordance with the definitionsset out below.

It must be noted that, as used in this specification and the appendedclaims, the singular forms “a,” “an,” and “the” include plural referentsunless the context clearly dictates otherwise.

As used herein, the terms “comprising,” “including,” “containing,”“characterized by,” and grammatical equivalents thereof are inclusive oropen-ended terms that do not exclude additional, unrecited elements ormethod steps.

As used herein, the phrase “consisting of” and grammatical equivalentsthereof exclude any element or step not specified in the claim.

As used herein, the phrase “consisting essentially of” and grammaticalequivalents thereof limit the scope of a claim to the specifiedmaterials or steps and those that do not materially affect the basic andnovel characteristic or characteristics of the claimed disclosure.

As used herein, the term “proximal” shall refer broadly to the conceptof a portion nearest an origin.

As used herein, the term “distal” shall generally refer to the oppositeof proximal, and thus to the concept of a portion farther from anorigin, or a furthest portion, depending upon the context.

As used herein, color sensors or multi spectrum sensors are thosesensors known to have a color filter array (CFA) thereon to filter theincoming electromagnetic radiation into its separate components. In thevisual range of the electromagnetic spectrum, such a CFA may be built ona Bayer pattern or modification thereon to separate green, red and bluespectrum components of the light.

As used herein, monochromatic sensor refers to an unfiltered imagingsensor. Since the pixels are color agnostic, the effective spatialresolution is appreciably higher than for their color (typicallyBayer-pattern filtered) counterparts in conventional single-sensorcameras. Monochromatic sensors may also have higher quantum efficiencybecause fewer incident photons are wasted between individual pixels.

As used herein, an emitter is a device that is capable of generating andemitting electromagnetic pulses. Various embodiments of emitters may beconfigured to emit pulses and have very specific frequencies or rangesof frequencies from within the entire electromagnetic spectrum. Pulsesmay comprise wavelengths from the visible and non-visible ranges. Anemitter may be cycled on and off to produce a pulse or may produce apulse with a shutter mechanism. An emitter may have variable poweroutput levels or may be controlled with a secondary device such as anaperture or filter. An emitter may emit broad spectrum or full spectrumelectromagnetic radiation that may produce pulses through colorfiltering or shuttering. An emitter may comprise a plurality ofelectromagnetic sources that act individually or in concert.

It should be noted that as used herein the term “light” is both aparticle and a wavelength and is intended to denote electromagneticradiation that is detectable by a pixel array 122 and may includewavelengths from the visible and non-visible spectrums ofelectromagnetic radiation. The term “partition” is used herein to mean apre-determined range of wavelengths of the electromagnetic spectrum thatis less than the entire spectrum, or in other words, wavelengths thatmake up some portion of the electromagnetic spectrum. As used herein, anemitter is a light source that may be controllable as to the portion ofthe electromagnetic spectrum that is emitted or that may operate as tothe physics of its components, the intensity of the emissions, or theduration of the emission, or all the above. An emitter may emit light inany dithered, diffused, or collimated emission and may be controlleddigitally or through analog methods or systems. As used herein, anelectromagnetic emitter is a source of a burst of electromagnetic energyand includes light sources, such as lasers, LEDs, incandescent light, orany light source that can be digitally controlled.

Referring now to the figures, FIG. 1 illustrates a schematic diagram ofa system 100 for sequential pulsed imaging in a light deficientenvironment. The system 100 can be deployed to generate an RGB imagewith specialty data overlaid on the RGB image. The system 100 includesan emitter 102 and a pixel array 122. The emitter 102 pulses a partitionof electromagnetic radiation in the light deficient environment 112 andthe pixel array 122 senses instances of reflected electromagneticradiation. The emitter 102 and the pixel array 122 work in sequence suchthat one or more pulses of a partition of electromagnetic radiationresults in image data sensed by the pixel array 122.

It should be noted that as used herein the term “light” is both aparticle and a wavelength and is intended to denote electromagneticradiation that is detectable by a pixel array 122 and may includewavelengths from the visible and non-visible spectrums ofelectromagnetic radiation. The term “partition” is used herein to mean apre-determined range of wavelengths of the electromagnetic spectrum thatis less than the entire spectrum, or in other words, wavelengths thatmake up some portion of the electromagnetic spectrum. As used herein, anemitter is a light source that may be controllable as to the portion ofthe electromagnetic spectrum that is emitted or that may operate as tothe physics of its components, the intensity of the emissions, or theduration of the emission, or all the above. An emitter may emit light inany dithered, diffused, or collimated emission and may be controlleddigitally or through analog methods or systems. As used herein, anelectromagnetic emitter is a source of a burst of electromagnetic energyand includes light sources, such as lasers, LEDs, incandescent light, orany light source that can be digitally controlled.

A pixel array 122 of an image sensor may be paired with the emitter 102electronically, such that the emitter 102 and the pixel array 122 aresynced during operation for both receiving the emissions and for theadjustments made within the system. The emitter 102 may be tuned to emitelectromagnetic radiation in the form of a laser, which may be pulsed toilluminate a light deficient environment 112. The emitter 102 may pulseat an interval that corresponds to the operation and functionality ofthe pixel array 122. The emitter 102 may pulse light in a plurality ofelectromagnetic partitions such that the pixel array receiveselectromagnetic energy and produces a dataset that corresponds in timewith each specific electromagnetic partition. For example, FIG. 1illustrates an implementation wherein the emitter 102 emits fourdifferent partitions of electromagnetic radiation, including red 104,green 106, blue 108 wavelengths, and a specialty 110 emission. Thespecialty 110 emission may include an excitation wavelength forfluorescing a reagent, a hyperspectral partition of electromagneticradiation, and/or a laser mapping pattern. The specialty 110 emissionmay include multiple separate emissions that are separate andindependent from one another. The specialty 110 emission may include acombination of an excitation wavelength for fluorescing a reagent and alaser mapping pattern, wherein the emissions are separate andindependent from one another. The data resulting from the separateemissions can be analyzed in tandem to identify a critical structurewithin a scene based on the fluorescence imaging data, and further toidentify the dimensions or positioning of the critical structure basedon the laser mapping data in combination with the fluorescence imagingdata. The specialty 110 emission may include a combination of ahyperspectral band of electromagnetic radiation and a laser mappingpattern, wherein the emissions are separate and independent from oneanother. The data resulting from the separate emissions can be analyzedin tandem to identify a critical structure within a scene based on thehyperspectral imaging data, and further to identify the dimensions orpositioning of the critical structure based on the laser mapping data incombination with the hyperspectral imaging data. In an embodiment, thespecialty 110 emission includes any desirable combination of emissionsthat may be combined with the data resulting from the pulsed red 104,pulsed green 106, and pulsed blue 108 emissions. The specialty 110emissions may be dispersed within a pulsing pattern such that thedifferent types of specialty 110 emissions are not pulsed as frequentlyas the pulsed red 104, pulsed green 106, and pulsed blue 108 emissions.

The light deficient environment 112 includes structures, tissues, andother elements that reflect a combination of red 114, green 116, and/orblue 118 light. A structure that is perceived as being red 114 willreflect back pulsed red 104 light. The reflection off the red structureresults in sensed red 105 by the pixel array 122 following the pulsedred 104 emission. The data sensed by the pixel array 122 results in ared exposure frame. A structure that is perceived as being green 116will reflect back pulsed green 106 light. The reflection off the greenstructure results in sensed green 107 by the pixel array 122 followingthe pulsed green 106 emission. The data sensed by the pixel array 122results in a green exposure frame. A structure that is perceived asbeing blue 118 will reflect back pulsed blue 108 light. The reflectionoff the blue structure results in sensed blue 109 by the pixel array 122following the pulsed blue 108 emission. The data sensed by the pixelarray 122 results in a blue exposure frame.

When a structure is a combination of colors, the structure will reflectback a combination of the pulsed red 104, pulsed green 106, and/orpulsed blue 108 emissions. For example, a structure that is perceived asbeing purple will reflect back light from the pulsed red 104 and pulsedblue 108 emissions. The resulting data sensed by the pixel array 122will indicate that light was reflected in the same region following thepulsed red 104 and pulsed blue 108 emissions. When the resultant redexposure frame and blue exposure frames are combined to form the RGBimage frame, the RGB image frame will indicate that the structure ispurple.

In an embodiment where the light deficient environment 112 includes afluorescent reagent or dye or includes one or more fluorescentstructures, tissues, or other elements, the pulsing scheme may includethe emission of a certain fluorescence excitation wavelength. Thecertain fluorescence excitation wavelength may be selected to fluorescea known fluorescent reagent, dye, or other structure. The fluorescentstructure will be sensitive to the fluorescence excitation wavelengthand will emit a fluorescence relaxation wavelength. The fluorescencerelaxation wavelength will be sensed by the pixel array 122 followingthe emission of the fluorescence excitation wavelength. The data sensedby the pixel array 122 results in a fluorescence exposure frame. Thefluorescence exposure frame may be combined with multiple other exposureframes to form an image frame. The data in the fluorescence exposureframe may be overlaid on an RGB image frame that includes data from ared exposure frame, a green exposure frame, and a blue exposure frame.

In an embodiment where the light deficient environment 112 includesstructures, tissues, or other materials that emit a spectral response tocertain partitions of the electromagnetic spectrum, the pulsing schememay include the emission of a hyperspectral partition of electromagneticradiation for the purpose of eliciting the spectral response from thestructures, tissues, or other materials present in the light deficientenvironment 112. The spectral response includes the emission orreflection of certain wavelengths of electromagnetic radiation. Thespectral response can be sensed by the pixel array 122 and result in ahyperspectral exposure frame. The hyperspectral exposure frame may becombined with multiple other exposure frames to form an image frame. Thedata in the hyperspectral exposure frame may be overlaid on an RGB imageframe that includes data from a red exposure frame, a green exposureframe, and a blue exposure frame.

In an embodiment, the pulsing scheme includes the emission of a lasermapping or tool tracking pattern. The reflected electromagneticradiation sensed by the pixel array 122 following the emission of thelaser mapping or tool tracking pattern results in a laser mappingexposure frame. The data in the laser mapping exposure frame may beprovided to a corresponding system to identify, for example, distancesbetween tools present in the light deficient environment 112, athree-dimensional surface topology of a scene in the light deficientenvironment 112, distances, dimensions, or positions of structures orobjects within the scene, and so forth. This data may be overlaid on anRGB image frame or otherwise provided to a user of the system.

The emitter 102 may be a laser emitter that is capable of emittingpulsed red 104 light for generating sensed red 105 data for identifyingred 114 elements within the light deficient environment 112. The emitter102 is further capable of emitting pulsed green 106 light for generatingsensed green 107 data for identifying green 116 elements within thelight deficient environment. The emitter 102 is further capable ofemitting pulsed blue 108 light for generating sensed blue 109 data foridentifying blue 118 elements within the light deficient environment.The emitter 102 is further capable of emitting a specialty 110 emissionfor mapping the topology 120 of a scene within the light deficientenvironment 112. The emitter 102 is capable of emitting the pulsed red104, pulsed green 106, pulsed blue 108, and pulsed specialty 110emissions in any desired sequence.

The pixel array 122 senses reflected electromagnetic radiation. Each ofthe sensed red 105, the sensed green 107, the sensed blue 109, and thesensed specialty 111 data can be referred to as an “exposure frame.” Thesensed specialty 111 may result in multiple separate exposure framesthat are separate and independent from one another. For example, thesensed specialty 111 may result in a fluorescence exposure frame, ahyperspectral exposure frame, and/or a laser mapping exposure framecomprising laser mapping data. Each exposure frame is assigned aspecific color or wavelength partition, wherein the assignment is basedon the timing of the pulsed color or wavelength partition from theemitter 102. The exposure frame in combination with the assignedspecific color or wavelength partition may be referred to as a dataset.Even though the pixels 122 are not color-dedicated, they can be assigneda color for any given dataset based on a priori information about theemitter.

For example, during operation, after pulsed red 104 light is pulsed inthe light deficient environment 112, the pixel array 122 sensesreflected electromagnetic radiation. The reflected electromagneticradiation results in an exposure frame, and the exposure frame iscatalogued as sensed red 105 data because it corresponds in time withthe pulsed red 104 light. The exposure frame in combination with anindication that it corresponds in time with the pulsed red 104 light isthe “dataset.” This is repeated for each partition of electromagneticradiation emitted by the emitter 102. The data created by the pixelarray 122 includes the sensed red 105 exposure frame identifying red 114components in the light deficient environment and corresponding in timewith the pulsed red 104 light. The data further includes the sensedgreen 107 exposure frame identifying green 116 components in the lightdeficient environment and corresponding in time with the pulsed green106 light. The data further includes the sensed blue 109 exposure frameidentifying blue 118 components in the light deficient environment andcorresponding in time with the pulsed blue 108 light. The data furtherincludes the sensed specialty 111 exposure frame identifying thetopology 120 and corresponding in time with the specialty 110 emission.

In one embodiment, three datasets representing RED, GREEN and BLUEelectromagnetic pulses are combined to form a single image frame. Thus,the information in a red exposure frame, a green exposure frame, and ablue exposure frame are combined to form a single RGB image frame. Oneor more additional datasets representing other wavelength partitions maybe overlaid on the single RGB image frame. The one or more additionaldatasets may represent, for example, the laser mapping data,fluorescence imaging data, and/or hyperspectral imaging data.

It will be appreciated that the disclosure is not limited to anyparticular color combination or any particular electromagneticpartition, and that any color combination or any electromagneticpartition may be used in place of RED, GREEN and BLUE, such as Cyan,Magenta and Yellow; Ultraviolet; infrared; any combination of theforegoing, or any other color combination, including all visible andnon-visible wavelengths, without departing from the scope of thedisclosure. In the figure, the light deficient environment 112 to beimaged includes red 114, green 116, and blue 118 portions, and furtherincludes a topology 120 that can be sensed and mapped into athree-dimensional rendering. As illustrated in the figure, the reflectedlight from the electromagnetic pulses only contains the data for theportion of the object having the specific color that corresponds to thepulsed color partition. Those separate color (or color interval)datasets can then be used to reconstruct the image by combining thedatasets at 126. The information in each of the multiple exposure frames(i.e., the multiple datasets) may be combined by a controller 124, acontrol unit, a camera control unit, the image sensor, an image signalprocessing pipeline, or some other computing resource that isconfigurable to process the multiple exposure frames and combine thedatasets at 126. The datasets may be combined to generate the singleimage frame within the endoscope unit itself or offsite by some otherprocessing resource.

FIG. 2 is a system 200 for providing illumination to a light deficientenvironment, such as for endoscopic imaging. The system 200 may be usedin combination with any of the systems, methods, or devices disclosedherein. The system 200 includes an emitter 202, a controller 204, ajumper waveguide 206, a waveguide connector 208, a lumen waveguide 210,a lumen 212, and an image sensor 214 with accompanying opticalcomponents (such as a lens). The emitter 202 (may be genericallyreferred to as a “light source”) generates light that travels throughthe jumper waveguide 206 and the lumen waveguide 210 to illuminate ascene at a distal end of the lumen 212. The emitter 202 may be used toemit any wavelength of electromagnetic energy including visiblewavelengths, infrared, ultraviolet, hyperspectral, fluorescenceexcitation, or other wavelengths. The lumen 212 may be inserted into apatient's body for imaging, such as during a procedure or examination.The light is output as illustrated by dashed lines 216. A sceneilluminated by the light may be captured using the image sensor 214 anddisplayed for a doctor or some other medical personnel. The controller204 may provide control signals to the emitter 202 to control whenillumination is provided to a scene. In one embodiment, the emitter 202and controller 204 are located within a camera control unit (CCU) orexternal console to which an endoscope is connected. If the image sensor214 includes a CMOS sensor, light may be periodically provided to thescene in a series of illumination pulses between readout periods of theimage sensor 214 during what is known as a blanking period. Thus, thelight may be pulsed in a controlled manner to avoid overlapping intoreadout periods of the image pixels in a pixel array of the image sensor214.

In one embodiment, the lumen waveguide 210 includes one or more opticalfibers. The optical fibers may be made of a low-cost material, such asplastic to allow for disposal of the lumen waveguide 210 and/or otherportions of an endoscope. In one embodiment, the lumen waveguide 210 isa single glass fiber having a diameter of 500 microns. The jumperwaveguide 206 may be permanently attached to the emitter 202. Forexample, a jumper waveguide 206 may receive light from an emitter withinthe emitter 202 and provide that light to the lumen waveguide 210 at thelocation of the connector 208. In one embodiment, the jumper waveguide106 includes one or more glass fibers. The jumper waveguide may includeany other type of waveguide for guiding light to the lumen waveguide210. The connector 208 may selectively couple the jumper waveguide 206to the lumen waveguide 210 and allow light within the jumper waveguide206 to pass to the lumen waveguide 210. In one embodiment, the lumenwaveguide 210 is directly coupled to a light source without anyintervening jumper waveguide 206.

The image sensor 214 includes a pixel array. In an embodiment, the imagesensor 214 includes two or more pixel arrays for generating athree-dimensional image. The image sensor 214 may constitute two moreimage sensors that each have an independent pixel array and can operateindependent of one another. The pixel array of the image sensor 214includes active pixels and optical black (“OB”) or optically blindpixels. The active pixels may be clear “color agnostic” pixels that arecapable of sensing imaging data for any wavelength of electromagneticradiation. The optical black pixels are read during a blanking period ofthe pixel array when the pixel array is “reset” or calibrated. In anembodiment, light is pulsed during the blanking period of the pixelarray when the optical black pixels are being read. After the opticalblack pixels have been read, the active pixels are read during a readoutperiod of the pixel array. The active pixels may be charged by theelectromagnetic radiation that is pulsed during the blanking period suchthat the active pixels are ready to be read by the image sensor duringthe readout period of the pixel array.

FIG. 2A is a schematic diagram of complementary system hardware such asa special purpose or general-purpose computer. Implementations withinthe scope of the present disclosure may also include physical and othernon-transitory computer readable media for carrying or storing computerexecutable instructions and/or data structures. Such computer readablemedia can be any available media that can be accessed by a generalpurpose or special purpose computer system. Computer readable media thatstores computer executable instructions are computer storage media(devices). Computer readable media that carry computer executableinstructions are transmission media. Thus, by way of example, and notlimitation, implementations of the disclosure can comprise at least twodistinctly different kinds of computer readable media: computer storagemedia (devices) and transmission media.

Computer storage media (devices) includes RAM, ROM, EEPROM, CD-ROM,solid state drives (“SSDs”) (e.g., based on RAM), Flash memory,phase-change memory (“PCM”), other types of memory, other optical diskstorage, magnetic disk storage or other magnetic storage devices, or anyother medium which can be used to store desired program code means inthe form of computer executable instructions or data structures andwhich can be accessed by a general purpose or special purpose computer.

A “network” is defined as one or more data links that enable thetransport of electronic data between computer systems and/or modulesand/or other electronic devices. In an implementation, a sensor andcamera control unit may be networked to communicate with each other, andother components, connected over the network to which they areconnected. When information is transferred or provided over a network oranother communications connection (either hardwired, wireless, or acombination of hardwired or wireless) to a computer, the computerproperly views the connection as a transmission medium. Transmissionsmedia can include a network and/or data links, which can be used tocarry desired program code means in the form of computer executableinstructions or data structures and which can be accessed by a generalpurpose or special purpose computer. Combinations of the above shouldalso be included within the scope of computer readable media.

Further, upon reaching various computer system components, program codemeans in the form of computer executable instructions or data structuresthat can be transferred automatically from transmission media tocomputer storage media (devices) (or vice versa). For example, computerexecutable instructions or data structures received over a network ordata link can be buffered in RAM within a network interface module(e.g., a “NIC”), and then eventually transferred to computer system RAMand/or to less volatile computer storage media (devices) at a computersystem. RAM can also include solid state drives (SSDs or PCIx based realtime memory tiered storage, such as FusionIO). Thus, it should beunderstood that computer storage media (devices) can be included incomputer system components that also (or even primarily) utilizetransmission media.

Computer executable instructions comprise, for example, instructions anddata which, when executed by one or more processors, cause ageneral-purpose computer, special purpose computer, or special purposeprocessing device to perform a certain function or group of functions.The computer executable instructions may be, for example, binaries,intermediate format instructions such as assembly language, or evensource code. Although the subject matter has been described in languagespecific to structural features and/or methodological acts, it is to beunderstood that the subject matter defined in the appended claims is notnecessarily limited to the described features or acts described above.Rather, the described features and acts are disclosed as example formsof implementing the claims.

Those skilled in the art will appreciate that the disclosure may bepracticed in network computing environments with many types of computersystem configurations, including, personal computers, desktop computers,laptop computers, message processors, control units, camera controlunits, hand-held devices, hand pieces, multi-processor systems,microprocessor-based or programmable consumer electronics, network PCs,minicomputers, mainframe computers, mobile telephones, PDAs, tablets,pagers, routers, switches, various storage devices, and the like. Itshould be noted that any of the above-mentioned computing devices may beprovided by or located within a brick and mortar location. Thedisclosure may also be practiced in distributed system environmentswhere local and remote computer systems, which are linked (either byhardwired data links, wireless data links, or by a combination ofhardwired and wireless data links) through a network, both performtasks. In a distributed system environment, program modules may belocated in both local and remote memory storage devices.

Further, where appropriate, functions described herein can be performedin one or more of: hardware, software, firmware, digital components, oranalog components. For example, one or more application specificintegrated circuits (ASICs) or field programmable gate arrays (FPGAs)can be programmed to carry out one or more of the systems and proceduresdescribed herein. Certain terms are used throughout the followingdescription and Claims to refer to particular system components. As oneskilled in the art will appreciate, components may be referred to bydifferent names. This document does not intend to distinguish betweencomponents that differ in name, but not function.

FIG. 2A is a block diagram illustrating an example computing device 250.Computing device 250 may be used to perform various procedures, such asthose discussed herein. Computing device 250 can function as a server, aclient, or any other computing entity. Computing device 250 can performvarious monitoring functions as discussed herein, and can execute one ormore application programs, such as the application programs describedherein. Computing device 250 can be any of a wide variety of computingdevices, such as a desktop computer, a notebook computer, a servercomputer, a handheld computer, camera control unit, tablet computer andthe like.

Computing device 250 includes one or more processor(s) 252, one or morememory device(s) 254, one or more interface(s) 256, one or more massstorage device(s) 258, one or more Input/Output (I/O) device(s) 260, anda display device 280 all of which are coupled to a bus 262. Processor(s)252 include one or more processors or controllers that executeinstructions stored in memory device(s) 254 and/or mass storagedevice(s) 258. Processor(s) 252 may also include various types ofcomputer readable media, such as cache memory.

Memory device(s) 254 include various computer readable media, such asvolatile memory (e.g., random access memory (RAM) 264) and/ornonvolatile memory (e.g., read-only memory (ROM) 266). Memory device(s)254 may also include rewritable ROM, such as Flash memory.

Mass storage device(s) 258 include various computer readable media, suchas magnetic tapes, magnetic disks, optical disks, solid-state memory(e.g., Flash memory), and so forth. As shown in FIG. 2, a particularmass storage device is a hard disk drive 274. Various drives may also beincluded in mass storage device(s) 258 to enable reading from and/orwriting to the various computer readable media. Mass storage device(s)258 include removable media 276 and/or non-removable media.

I/O device(s) 260 include various devices that allow data and/or otherinformation to be input to or retrieved from computing device 250.Example I/O device(s) 260 include digital imaging devices,electromagnetic sensors and emitters, cursor control devices, keyboards,keypads, microphones, monitors or other display devices, speakers,printers, network interface cards, modems, lenses, CCDs or other imagecapture devices, and the like.

Display device 280 includes any type of device capable of displayinginformation to one or more users of computing device 250. Examples ofdisplay device 280 include a monitor, display terminal, video projectiondevice, and the like.

Interface(s) 256 include various interfaces that allow computing device250 to interact with other systems, devices, or computing environments.Example interface(s) 256 may include any number of different networkinterfaces 270, such as interfaces to local area networks (LANs), widearea networks (WANs), wireless networks, and the Internet. Otherinterface(s) include user interface 268 and peripheral device interface272. The interface(s) 256 may also include one or more user interfaceelements 268. The interface(s) 256 may also include one or moreperipheral interfaces such as interfaces for printers, pointing devices(mice, track pad, etc.), keyboards, and the like.

Bus 262 allows processor(s) 252, memory device(s) 254, interface(s) 256,mass storage device(s) 258, and I/O device(s) 260 to communicate withone another, as well as other devices or components coupled to bus 262.Bus 262 represents one or more of several types of bus structures, suchas a system bus, PCI bus, IEEE 1394 bus, USB bus, and so forth.

For purposes of illustration, programs and other executable programcomponents are shown herein as discrete blocks, although it isunderstood that such programs and components may reside at various timesin different storage components of computing device 250 and are executedby processor(s) 252. Alternatively, the systems and procedures describedherein can be implemented in hardware, or a combination of hardware,software, and/or firmware. For example, one or more application specificintegrated circuits (ASICs) or field programmable gate arrays (FPGAs)can be programmed to carry out one or more of the systems and proceduresdescribed herein.

FIG. 3A illustrates the operational cycles of a sensor used in rollingreadout mode or during the sensor readout 300. The frame readout maystart at and may be represented by vertical line 310. The read-outperiod is represented by the diagonal or slanted line 302. The activepixels of the pixel array of the image sensor may be read out on a rowby row basis, the top of the downwards slanted edge being the sensor toprow 312 and the bottom of the downwards slanted edge being the sensorbottom row 314. The time between the last row readout and the nextreadout cycle may be called the blanking period 316. It should be notedthat some of the sensor pixel rows might be covered with a light shield(e.g., a metal coating or any other substantially black layer of anothermaterial type). These covered pixel rows may be referred to as opticalblack rows 318 and 320. Optical black rows 318 and 320 may be used asinput for correction algorithms. As shown in FIG. 3A, these opticalblack rows 318 and 320 may be located on the top of the pixel array orat the bottom of the pixel array or at the top and the bottom of thepixel array.

FIG. 3B illustrates a process of controlling the amount ofelectromagnetic radiation, e.g., light, that is exposed to a pixel,thereby integrated or accumulated by the pixel. It will be appreciatedthat photons are elementary particles of electromagnetic radiation.Photons are integrated, absorbed, or accumulated by each pixel andconverted into an electrical charge or current. An electronic shutter orrolling shutter (shown by dashed line 322) may be used to start theintegration time by resetting the pixel. The light will then integrateuntil the next readout phase. The position of the electronic shutter 322can be moved between two readout cycles 302 to control the pixelsaturation for a given amount of light. It should be noted that thistechnique allows for a constant integration time between two differentlines but introduces a delay when moving from top to bottom rows.

FIG. 3C illustrates the case where the electronic shutter 322 has beenremoved. In this configuration, the integration of the incoming lightmay start during readout 302 and may end at the next readout cycle 302,which also defines the start of the next integration.

FIG. 3D shows a configuration without an electronic shutter 322, butwith a controlled and pulsed light 330 during the blanking period 316.This ensures that all rows see the same light issued from the same lightpulse 330. In other words, each row will start its integration in a darkenvironment, which may be at the optical black back row 320 of read outframe (m) for a maximum light pulse width, and will then receive a lightstrobe and will end its integration in a dark environment, which may beat the optical black front row 318 of the next succeeding read out frame(m+1) for a maximum light pulse width. In the FIG. 3D example, the imagegenerated from the light pulse will be solely available during frame(m+1) readout without any interference with frames (m) and (m+2). Itshould be noted that the condition to have a light pulse to be read outonly in one frame and not interfere with neighboring frames is to havethe given light pulse firing during the blanking period 316. Because theoptical black rows 318, 320 are insensitive to light, the optical blackback rows 320 time of frame (m) and the optical black front rows 318time of frame (m+1) can be added to the blanking period 316 to determinethe maximum range of the firing time of the light pulse 330.

As illustrated in the FIG. 3A, a sensor may be cycled many times toreceive data for each pulsed color or wavelength (e.g., Red, Green,Blue, or other wavelength on the electromagnetic spectrum). Each cyclemay be timed. In an embodiment, the cycles may be timed to operatewithin an interval of 16.67 ms. In another embodiment, the cycles may betimed to operate within an interval of 8.3 ms. It will be appreciatedthat other timing intervals are contemplated by the disclosure and areintended to fall within the scope of this disclosure.

FIG. 4A graphically illustrates the operation of an embodiment of anelectromagnetic emitter. An emitter may be timed to correspond with thecycles of a sensor, such that electromagnetic radiation is emittedwithin the sensor operation cycle and/or during a portion of the sensoroperation cycle. FIG. 4A illustrates Pulse 1 at 402, Pulse 2 at 404, andPulse 3 at 406. In an embodiment, the emitter may pulse during thereadout period 302 of the sensor operation cycle. In an embodiment, theemitter may pulse during the blanking portion 316 of the sensoroperation cycle. In an embodiment, the emitter may pulse for a durationthat is during portions of two or more sensor operational cycles. In anembodiment, the emitter may begin a pulse during the blanking portion316, or during the optical black portion 320 of the readout period 302,and end the pulse during the readout period 302, or during the opticalblack portion 318 of the readout period 302 of the next succeedingcycle. It will be understood that any combination of the above isintended to fall within the scope of this disclosure as long as thepulse of the emitter and the cycle of the sensor correspond.

FIG. 4B graphically represents varying the duration and magnitude of theemitted electromagnetic pulse (e.g., Pulse 1 at 412, Pulse 2 at 414, andPulse 3 at 416) to control exposure. An emitter having a fixed outputmagnitude may be pulsed during any of the cycles noted above in relationto FIGS. 3D and 4A for an interval to provide the needed electromagneticenergy to the pixel array. An emitter having a fixed output magnitudemay be pulsed at a longer interval of time, thereby providing moreelectromagnetic energy to the pixels or the emitter may be pulsed at ashorter interval of time, thereby providing less electromagnetic energy.Whether a longer or shorter interval time is needed depends upon theoperational conditions.

In contrast to adjusting the interval of time the emitter pulses a fixedoutput magnitude, the magnitude of the emission itself may be increasedto provide more electromagnetic energy to the pixels. Similarly,decreasing the magnitude of the pulse provides less electromagneticenergy to the pixels. It should be noted that an embodiment of thesystem may have the ability to adjust both magnitude and durationconcurrently, if desired. Additionally, the sensor may be adjusted toincrease its sensitivity and duration as desired for optimal imagequality. FIG. 4B illustrates varying the magnitude and duration of thepulses. In the illustration, Pulse 1 at 412 has a higher magnitude orintensity than either Pulse 2 at 414 or Pulse 3 at 416. Additionally,Pulse 1 at 412 has a shorter duration than Pulse 2 at 414 or Pulse 3 at416, such that the electromagnetic energy provided by the pulse isillustrated by the area under the pulse shown in the illustration. Inthe illustration, Pulse 2 at 414 has a relatively low magnitude orintensity and a longer duration when compared to either Pulse 1 at 412or Pulse 3 at 416. Finally, in the illustration, Pulse 3 at 416 has anintermediate magnitude or intensity and duration, when compared to Pulse1 at 412 and Pulse 2 at 414.

FIG. 5 is a graphical representation of an embodiment of the disclosurecombining the operational cycles, the electromagnetic emitter, and theemitted electromagnetic pulses of FIGS. 3A-3D and 4A to demonstrate theimaging system during operation in accordance with the principles andteachings of the disclosure. As can be seen in the figure, theelectromagnetic emitter pulses the emissions primarily during theblanking period 316 of the image sensor such that the pixels will becharged and ready to read during the readout period 302 of the imagesensor cycle. The dashed lines in FIG. 5 represent the pulses ofelectromagnetic radiation (from FIG. 4A). The pulses of electromagneticradiation are primarily emitted during the blanking period 316 of theimage sensor but may overlap with the readout period 302 of the imagesensor.

An exposure frame includes the data read by the pixel array of the imagesensor during a readout period 302. The exposure frame may be combinedwith an indication of what type of pulse was emitted by the emitterprior to the readout period 302. The combination of the exposure frameand the indication of the pulse type may be referred to as a dataset.Multiple exposure frames may be combined to generate a black-and-whiteor RGB color image. Additionally, hyperspectral, fluorescence, and/orlaser mapping imaging data may be overlaid on a black-and-white or RGBimage.

In an embodiment, an RGB image frame is generated based on threeexposure frames, including a red exposure frame generated by the imagesensor subsequent to a red emission, a green exposure frame generated bythe image sensor subsequent to a green emission, and a blue exposureframe generated by the image sensor subsequent to a blue emission.Fluorescence imaging data may be overlaid on the RGB image frame. Thefluorescence imaging data may be drawn from one or more fluorescenceexposure frames. A fluorescence exposure frame includes data generatedby the image sensor during the readout period 302 subsequent to emissionof an excitation wavelength of electromagnetic radiation for exciting afluorescent reagent. The data sensed by the pixel array subsequent tothe excitation of the fluorescent reagent may be the relaxationwavelength emitted by the fluorescent reagent. The fluorescence exposureframe may include multiple fluorescence exposure frames that are eachgenerated by the image sensor subsequent to a different type offluorescence excitation emission. In an embodiment, the fluorescenceexposure frame includes multiple fluorescence exposure frames, includinga first fluorescence exposure frame generated by the image sensorsubsequent to an emission of electromagnetic radiation with a wavelengthfrom about 770 nm to about 790 and a second fluorescence exposure framegenerated by the image sensor subsequent to an emission ofelectromagnetic radiation with a wavelength from about 795 nm to about815 nm. The fluorescence exposure frame may include further additionalfluorescence exposure frames that are generated by the image sensorsubsequent to other fluorescence excitation emissions of light as neededbased on the imaging application.

In an embodiment, an exposure frame is the data sensed by the pixelarray during the readout period 302 that occurs subsequent to a blankingperiod 316. The emission of electromagnetic radiation is emitted duringthe blanking period 316. In an embodiment, a portion of the emission ofelectromagnetic radiation overlaps the readout period 316. The blankingperiod 316 occurs when optical black pixels of the pixel array are beingread and the readout period 302 occurs when active pixels of the pixelarray are being read. The blanking period 316 may overlap the readoutperiod 302.

FIGS. 6A and 6B illustrate processes for recording an image frame.Multiple image frames may be strung together to generate a video stream.A single image frame may include data from multiple exposure frames,wherein an exposure frame is the data sensed by a pixel array subsequentto an emission of electromagnetic radiation. FIG. 6A illustrates atraditional process that is typically implemented with a color imagesensor having a color filter array (CFA) for filtering out certainwavelengths of light per pixel. FIG. 6B is a process that is disclosedherein and can be implemented with a monochromatic “color agnostic”image sensor that is receptive to all wavelengths of electromagneticradiation.

The process illustrated in FIG. 6A occurs from time t(0) to time t(1).The process begins with a white light emission 602 and sensing whitelight 604. The image is processed and displayed at 606 based on thesensing at 604.

The process illustrated in FIG. 6B occurs from time t(0) to time t(1).The process begins with an emission of green light 612 and sensingreflected electromagnetic radiation 614 subsequent to the emission ofgreen light 612. The process continues with an emission of red light 616and sensing reflected electromagnetic radiation 618 subsequent to theemission of red light 616. The process continues with an emission ofblue light 620 and sensing reflected electromagnetic radiation 622subsequent to the emission of blue light 620. The process continues withone or more emissions of a specialty 624 emission and sensing reflectedelectromagnetic energy 626 subsequent to each of the one or moreemissions of the specialty 624 emission. The specialty emission mayinclude one or more separate emissions such as an excitation wavelengthof a fluorescent reagent, a hyperspectral emission, and/or a lasermapping emission. Each of the separate multiple specialty emissions maybe independently sensed by the image sensor to generate separate andindependent exposure frames. The image is processed and displayed at 628based on each of the sensed reflected electromagnetic energy instances614, 618, 622, and 626.

The process illustrated in FIG. 6B provides a higher resolution imageand provides a means for generating an RGB image that further includesspecialty data. When partitioned spectrums of light are used, (as inFIG. 6B) a sensor can be made sensitive to all wavelengths ofelectromagnetic energy. In the process illustrated in FIG. 6B, themonochromatic pixel array is instructed that it is sensingelectromagnetic energy from a predetermined partition of the fullspectrum of electromagnetic energy in each cycle. Therefore, to form animage the sensor need only be cycled with a plurality of differingpartitions from within the full spectrum of light. The final image isassembled based on the multiple cycles. Because the image from eachcolor partition frame cycle has a higher resolution (compared with a CFApixel array), the resultant image created when the partitioned lightframes are combined also has a higher resolution. In other words,because each and every pixel within the array (instead of, at most,every second pixel in a sensor with a CFA) is sensing the magnitudes ofenergy for a given pulse and a given scene, just fractions of timeapart, a higher resolution image is created for each scene.

As can be seen graphically in the embodiments illustrated in FIGS. 6Aand 6B between times t(0) and t(1), the sensor for the partitionedspectrum system in FIG. 6B has cycled at least four times for every oneof the full spectrum system in FIG. 6A. In an embodiment, a displaydevice (LCD panel) operates at 50-60 frames per second. In such anembodiment, the partitioned light system in FIG. 6B may operate at200-240 frames per second to maintain the continuity and smoothness ofthe displayed video. In other embodiments, there may be differentcapture and display frame rates. Furthermore, the average capture ratecould be any multiple of the display rate.

In an embodiment, it may be desired that not all partitions berepresented equally within the system frame rate. In other words, notall light sources have to be pulsed with the same regularity so as toemphasize and de-emphasize aspects of the recorded scene as desired bythe users. It should also be understood that non-visible and visiblepartitions of the electromagnetic spectrum may be pulsed together withina system with their respective data value being stitched into the videooutput as desired for display to a user.

An example embodiment may comprise a pulse cycle pattern as follows:

i. Green pulse;

ii. Red pulse;

iii. Blue pulse;

iv. Green pulse;

v. Red pulse;

vi. Blue pulse;

vii. Laser mapping pulsing scheme;

viii. Fluorescence excitation pulse;

ix. Hyperspectral pulse;

x. (Repeat)

A further example embodiment may comprise a pulse cycle pattern asfollows:

i. Green pulse;

ii. Red pulse;

iii. Blue pulse;

iv. Fluorescence excitation pulse;

v. Hyperspectral pulse;

vi. Green pulse;

vii. Red pulse;

viii. Blue pulse;

ix. Fluorescence excitation pulse;

x. Hyperspectral pulse;

xi. Laser mapping pulsing scheme;

xii. (Repeat)

The pulsing pattern may be altered to suit the imaging objectives for aspecific implementation. An example imaging objective is to obtainhyperspectral imaging data and fluorescence imaging data, and further toobtain laser mapping and/or tool tracking data that is based on analysisof the hyperspectral and/or fluorescence imaging data. In such anexample, the laser mapping and/or tool tracking data may be analyzed forcertain areas of a scene that have been highlighted by the hyperspectraland/or fluorescence imaging data. A further example imaging objective isto obtain hyperspectral imaging data or fluorescence imaging data, andfurther to obtain laser mapping and/or tool tracking data. A furtherexample imaging objective is to obtain laser mapping and/or tooltracking data. A further example imaging objective is to obtainhyperspectral imaging data. A further example imaging objective is toobtain fluorescence imaging data. It should be appreciated that theimaging objective may be specialized depending on the reason fordeploying the imaging system. Additionally, the imaging objective maychange during a single imaging session, and the pulsing pattern may bealtered to match the changing imaging objectives.

As can be seen in the example, a laser mapping partition may be pulsedat a rate differing from the rates of the other partition pulses. Thismay be done to emphasize a certain aspect of the scene, with the lasermapping data simply being overlaid with the other data in the videooutput to make the desired emphasis. It should be noted that theaddition of a laser mapping partition on top of the RED, GREEN, and BLUEpartitions does not necessarily require the serialized system to operateat four times the rate of a full spectrum non-serial system becauseevery partition does not have to be represented equally in the pulsepattern. As seen in the embodiment, the addition of a partition pulsethat is represented less in a pulse pattern (laser mapping in the aboveexample), would result in an increase of less than 20% of the cyclingspeed of the sensor to accommodate the irregular partition sampling.

In various embodiments, the pulse cycle pattern may further include anyof the following wavelengths in any suitable order. Such wavelengths maybe particularly suited for exciting a fluorescent reagent to generatefluorescence imaging data by sensing the relaxation emission of thefluorescent reagent based on a fluorescent reagent relaxation emission:

i. 770±20 nm;

ii. 770±10 nm;

iii. 770±5 nm;

iv. 790±20 nm;

v. 790±10 nm;

vi. 790±5 nm;

vii. 795±20 nm;

viii. 795±10 nm;

ix. 795±5 nm;

x. 815±20 nm;

xi. 815±10 nm;

xii. 815±5 nm;

xiii. 770 nm to 790 nm; and/or xiv. 795 nm to 815 nm.

In various embodiments, the pulse cycle may further include any of thefollowing wavelengths in any suitable order. Such wavelengths may beparticularly suited for generating hyperspectral imaging data:

i. 513 nm to 545 nm;

ii. 565 nm to 585 nm;

iii. 900 nm to 1000 nm;

iv. 513±5 nm;

v. 513±10 nm;

vi. 513±20 nm;

vii. 513±30 nm;

viii. 513±35 nm;

ix. 545±5 nm;

x. 545±10 nm;

xi. 545±20 nm;

xii. 545±30 nm;

xiii. 545±35 nm;

xiv. 565±5 nm;

xv. 565±10 nm;

xvi. 565±20 nm;

xvii. 565±30 nm;

xviii. 565±35 nm;

xix. 585±5 nm;

xx. 585±10 nm;

xxi. 585±20 nm;

xxii. 585±30 nm;

xxiii. 585±35 nm;

xxiv. 900±5 nm;

xxv. 900±10 nm;

xxvi. 900±20 nm;

xxvii. 900±30 nm;

xxviii. 900±35 nm;

xxix. 1000±5 nm;

xxx. 1000±10 nm;

xxxi. 1000±20 nm;

xxxii. 1000±30 nm; or xxxiii. 1000±35 nm.

The partition cycles may be divided so as to accommodate or approximatevarious imaging and video standards. In an embodiment, the partitioncycles may comprise pulses of electromagnetic energy in the Red, Green,and Blue spectrum as follows as illustrated best in FIGS. 7A-7D. In FIG.7A, the different light intensities have been achieved by modulating thelight pulse width or duration within the working range shown by thevertical grey dashed lines. In FIG. 7B, the different light intensitieshave been achieved by modulating the light power or the power of theelectromagnetic emitter, which may be a laser or LED emitter, butkeeping the pulse width or duration constant. FIG. 7C shows the casewhere both the light power and the light pulse width are beingmodulated, leading to greater flexibility. The partition cycles may useCyan Magenta Yellow (CMY), infrared, ultraviolet, hyperspectral, andfluorescence using a non-visible pulse source mixed with visible pulsesources and any other color space required to produce an image orapproximate a desired video standard that is currently known or yet tobe developed. It should also be understood that a system may be able toswitch between the color spaces on the fly to provide the desired imageoutput quality.

In an embodiment using color spaces Green-Blue-Green-Red (as seen inFIG. 7D) it may be desirous to pulse the luminance components more oftenthan the chrominance components because users are generally moresensitive to light magnitude differences than to light colordifferences. This principle can be exploited using a mono-chromaticsensor as illustrated in FIG. 7D. In FIG. 7D, green, which contains themost luminance information, may be pulsed more often or with moreintensity in a (G B G R G B G R . . . ) scheme to obtain the luminancedata. Such a configuration would create a video stream that hasperceptively more detail, without creating and transmittingunperceivable data.

In an embodiment, duplicating the pulse of a weaker partition may beused to produce an output that has been adjusted for the weaker pulse.For example, blue laser light is considered weak relative to thesensitivity of silicon-based pixels and is difficult to produce incomparison to the red or green light, and therefore may be pulsed moreoften during a frame cycle to compensate for the weakness of the light.These additional pulses may be done serially over time or by usingmultiple lasers that simultaneously pulse to produce the desiredcompensation effect. It should be noted that by pulsing during ablanking period (time during which the sensor is not reading out thepixel array), the sensor is insensitive to differences/mismatchesbetween lasers of the same kind and simply accumulates the light for thedesired output. In another embodiment, the maximum light pulse range maybe different from frame to frame. This is shown in FIG. 7E, where thelight pulses are different from frame to frame. The sensor may be builtto be able to program different blanking periods with a repeatingpattern of two or three or four or n frames. In FIG. 7E, four differentlight pulses are illustrated, and Pulse 1 may repeat for example afterPulse 4 and may have a pattern of four frames with different blankingperiods. This technique can be used to place the most powerful partitionon the smallest blanking period and therefore allow the weakestpartition to have wider pulse on one of the next frames without the needof increasing the readout speed. The reconstructed frame can still havea regular pattern from frame to frame as it is constituted of manypulsed frames.

Referring now to FIGS. 8A and 8B, implementations of image sensors areillustrated. The image sensor illustrated in FIG. 8A is a traditionalimage sensor 800 including a pixel array common in the prior art. Theminimal area image sensor 820 illustrated in FIG. 8B is a pixel array inaccordance with the teachings and principles of the disclosure. Theminimal area image sensor 820 may be used in a distal tip of anendoscope. The distal tip of an endoscope is necessarily small becausethe distal tip is usually inserted in small areas such as body cavities.The distal tip of an endoscope is often too small to accommodate atraditional image sensor 800.

In a space-constrained environment such as the distal tip of anendoscope, it may be desirable to reduce non-sensitive portions of animage sensor to maximize the area of the image sensor that is devoted tolight sensing elements. This can reduce the total area of the imagesensor while preserving image quality. One implementation for reducingthe non-light sensing elements in the image sensor is to eliminate orreduce the number of optical black (“OB”) rows in the image sensor.However, eliminating the optical black rows can also eliminate thepossibility of implementing an OB-based column fixed pattern noisecancellation method that is commonly used in conventional imagingsystems. Column fixed pattern noise cancellation requires black pixeldata with typically 10 to 100 black pixels per column. The black pixelscorrect for a column-wise random offset prior to reading out lightsensing pixels. Disclosed herein are alternative methods, systems, anddevices for correcting for fixed pattern noise when using a minimal areaimage sensor 820.

Image sensors can incorporate special purpose, optically blind oroptical black (“OB”) rows and/or columns. Optical black pixels mayalternatively be referred to as manufacturing buffer pixels or dummypixels. An optical black row 804 is located at the top and/or bottom ofa record area 802. The record area 802 includes the imaging pixel array.An optical black column 806 is located to the right and/or left of thepixel array. The optical black rows and columns are used to offsetcalibration of the record area 802.

The example layout of the traditional image sensor 800 includes anoptical black row 804 on the top and bottom of the traditional recordarea 802. The traditional image sensor 800 further includes an opticalblack column 806 on the left and right sides of the record area 802. Theexample layout of the minimal area image sensor 820 includes opticalblack columns 806 on the left and right sides of the record area 802.The minimal area image sensor 820 does not include any optical blackrows 804. Each of the example embodiments may include a guard ring 808surrounding the circumference of the image sensor 800, 820.

The optical black rows 804 may be used to monitor the analog pixel blacklevel for purposes of an optical black clamp algorithm. The opticalblack rows 804 may also be used by a digital algorithm for the purposeof cancelling column fixed pattern noise (CFPN). The optical blackcolumns 806 may be used to assess the line offset as a means to cancelout line noise in the record area 802. Because line noise can betemporal, the line offset may be computed anew for each line of therecord area 802 in every frame.

The minimal area image sensor 820 provides an overall reduction in thesize of the image sensor by removing the optical black rows 804 from thetop and bottom sides of the record area 802. When deploying the minimalarea image sensor 820, the optical black columns 806 are used for theoptical black clamp algorithm rather than any optical black rows 804. Inan embodiment, all fixed pattern noise, including column fixed patternnoise, can be cancelled by acquiring frames of dark data. This negatesthe need for a dedicated CFPN correction and its associated opticalblack rows 804.

The number of optical black columns 806 might typically be 100 or moredepending on space constraints. The more optical black columns 806 thatare available, the greater the line-offset precision may be. Greaterprecision means lower line noise post-correction. Normally, allavailable physical optical black pixels are read for each line as shownin FIG. 9. A further degree of pixel array size reduction can beachieved if, instead of having the requisite number of physical opticalblack pixels, (given a certain precision target), a smaller number ofphysical optical black pixels are implemented and the physical opticalblack pixels are resampled multiple times during the horizontal readoutprocess of the record area 802 and the optical black columns 806. Thisapproach is illustrated in FIG. 10.

In an alternative embodiment, a minimal area image sensor includesoptical black rows 804 but does not include optical black columns 806.In such an embodiment, the optical black rows 804 may be read before andafter reading the active pixels in the record area 802 of the pixelarray.

The disclosures provided herein may be applied to all forms of fixedpattern noise and are not necessarily restricted to cancelling columnfixed pattern noise. Other types of fixed pattern noise may be cancelledby acquiring frames of dark data to negate the need for a dedicatedcolumn fixed pattern noise correction with its associated optical blackrows. In an embodiment, an off-sensor frame of memory is used forstoring each pixel's calibration data and subsequently cancelling allsources of fixed pattern noise at the pixel level. Although more memorymay be needed for a black frame calibration than for a column fixedpattern noise algorithm, there may be an advantage in that all sourcesof fixed pattern noise can be eliminated or significantly mitigated byway of the methods, systems, and devices disclosed herein. Examplesources of fixed pattern noise that can be eliminated or mitigated byway of the disclosures herein include column fixed pattern noise, pixelfixed pattern noise, and row fixed pattern noise.

FIG. 9 illustrates a readout sequence 908 for a pixel array common inthe prior art. As shown in FIG. 9, the readout sequence 908 begins withcolumn readout 906 for each of the optical black columns 904. Theoptical black columns 904 may be similar to those optical black columns806 illustrated in FIGS. 8A and 8B. Upon completion of the columnreadout 906 for the optical black columns 904, the readout sequence 908begins the column readout 906 for the record area 910. The record area910 may be similar to the record area 802 illustrated in FIGS. 8A and8B. The record area 910 may include clear pixels 902 or color agnosticpixels. The readout sequence 908 continues until the entire record area910 has been read. After the record area 910 has been read, the opticalblack columns 904 on the opposite side are read. The readout sequence908 continues line-by-line until every row of the pixel array has beenread.

FIG. 10 illustrates a readout sequence 1008 for a pixel array having anarea size reduction that reduces the number of optical black pixels. Inthe readout sequence 1008 illustrated in FIG. 10, the optical blackcolumns 1004 undergo column readout 1006 multiple times. As shown inFIG. 10, the optical black column 1004 readout can be resampled m timeor n times. The record area may include clear pixels 1002.

Raw CMOS image sensor data present at the output of the digitizer may befar from ideal. It may often be the case that the optimal order withwhich to read out a horizontal row of pixels does not equate to theactual physical order within the array. Also, raw data often revealsundesirable artifacts that reflect the nature of the readoutarchitecture. These readout artifacts may include column fixed patternnoise arising from the variation in offset from column to column and mayfurther include temporal line noise resulting from circuit resetsassociated with the horizontal readout process.

Another property of CMOS (Complementary Metal Oxide Semiconductor)sensors is that a degree of dark signal may be generated by thephotodiode within the pixel. The amount of integrated signal arisingfrom dark signal depends on exposure time and temperature. Because thedark signal may be indistinguishable from photo-signal, changes in thedark signal translate to changes in signal pedestal in the analogdomain. Therefore, it may be important to sample and adjust for the darksignal so the available dynamic range of the analog to digital convertercan be fully exploited.

FIG. 11 is a graphical representation of a simple exponential smoothing(SES) pixel offset estimation with small and large values for w. SESpixel offset estimation can be implemented to reduce or eliminate fixedpattern noise in exposure frames.

Exponential smoothing is a timeseries forecasting method. Exponentialsmoothing results in a prediction that is a weighted sum of pastobservations, wherein the weights decay exponentially as pastobservations get older. In an embodiment, SES is used to generate areference frame based on a plurality of dark exposure frames. Each ofthe plurality of dark exposure frames is generated by the pixel arrayand includes dark frame data that is sensed when the emitter is notemitting electromagnetic radiation. The reference frame may be appliedto reduce fixed pattern noise in exposure frames and/or image framesgenerated by the image sensor. SES is used to increase the precision ofthe reference frame. In an embodiment, the SES algorithm explicitly usesan exponentially decreasing weight for factoring in previously captureddark exposure frames.

In an embodiment, SES is applied to dark frame data from a plurality ofdark exposure frames. SES is used to generate a reference frame based onthe dark frame data captured in the plurality of dark exposure frames.The reference frame does not include imaging data that is displayed on ascreen or otherwise provided to a user, and instead includes data thatis used to remove fixed pattern noise from exposure frames and/or imageframes. The reference frame is calculated by applying SES to theplurality of dark exposure frames. The plurality of dark exposure framesare captured over time and older dark exposure frames are given lessweight when calculating the reference frame. The reference frameincludes reference data that is subtracted from exposure frames and/orimage frames in furtherance of reducing fixed pattern noise. Each of theplurality of dark exposure frames is sensed by the pixel array when alight deficient environment is dark, and an emitter is not pulsingelectromagnetic radiation.

In an embodiment, an emitter emits pulses of electromagnetic radiationin a pattern that includes varying wavelengths of electromagneticradiation. In an embodiment, the pattern includes red, green, blue, andlaser mapping wavelengths of electromagnetic radiation. The pattern mayfurther include instances wherein the emitter is not emittingelectromagnetic radiation. The pixel array can be configured to sensedark frame data when the emitter is not emitting electromagneticradiation. When the pixel array senses dark frame data, this results ina dark exposure frame. In an embodiment, the pattern of varyingwavelengths of electromagnetic radiation further includes instanceswherein the emitter is not emitting electromagnetic radiation. The pixelarray generates an exposure frame in response to each emission ofelectromagnetic radiation, and additionally generates a dark exposureframe in response to an instance wherein the emitter is not emittingelectromagnetic radiation. The exposure frames and dark exposure framesmay be captured in a repeating pattern over time such that the darkexposure frames are interspersed between (non-dark) exposure frames. Aseries of exposure frames may be combined to generate an image frame,and in an embodiment, there is a dark exposure frame corresponding witheach image frame or grouping of image frames. The series of darkexposure frames are used to generate a reference frame, and thereference frame is used to reduce the fixed pattern noise present in theexposure frames (and image frames). SES is applied to the series of darkexposure frames such that older dark exposure frames have lesser weightthan newer dark exposure frames.

In an embodiment, a single reference frame is incrementally adjustedeach time a dark exposure frame is sensed by the pixel array. Each pixelsample taken in the dark exposure frame is divided by an appropriatebinary number (2^(w)) before being added to the buffer content andmultiplied by (2^(w)−1)/2^(w). FIG. 11 graphically illustrates theimpact on the pixel offset estimate for small values of w and largevalues of w. As shown in FIG. 11, high values of w result in greaterstatistical precision over time in a stable scenario. Lower values of wcause the SES correction to be more reactive to rapid changes at theexpense of precision and stability. In an embodiment, the value of w istunable via control registers in communication with the endoscopicsystem.

In an embodiment, dark current temperature dependence can be overcome byusing a running average calibration as described herein. In a rollingshutter operation, pixel integration time may be changed on aframe-to-frame basis to accommodate light environment changes controlledby an auto exposure algorithm. For example, the frame readout sequenceillustrated in FIGS. 3A-3D illustrate an electronic shutter beingadjusted within the frame to control integration time. Because thecalibration may be performed at a given integration time, the dark framecorrection algorithm may lose efficacy and become inaccurate when tryingto correct frames with different integration time. One implementation ofthe disclosure to overcome this issue is to introduce a secondcalibration point per pixel. This may require a second frame of memory.The second calibration point for each pixel may be collected at adifferent integration time. Pixel calibration data at a givenintegration time may be computed using linear interpolation. However,the use of linear interpolation can introduce interpolation error andcomplicate backend processing of the image data.

When pulsing light in a light deficient environment, the pixelintegration time may be substantially constant from frame to frame. Thisis illustrated especially in FIG. 3D, where light intensity is adjustedby changing the light pulse width or level. In this implementation, onlyone integration time calibration may be required, and interpolation maynot be needed. In an embodiment, dark frame subtraction can be used toadjust for the average offset of each pixel. This can suppress all formsof fixed pattern noise. Because the pixel offsets have temperaturedependence, the correction can be a running average process by takingsample dark frames at regular intervals and updating stored correctiondata based on the samples. The resultant quality of this correction maydepend on the sampling statistics.

In an embodiment, the uncertainty of a pixel offset estimate is equal tothe temporal noise of that pixel divided by the square root of thenumber of samples. This uncertainty may directly translate topost-correction pixel fixed pattern noise and is independent of theoriginal fixed pattern noise. In an embodiment where a video stream iscaptured at the rate of 60 image frames per second, the pixel fixedpattern noise may be less than one-fourth of the pixel temporal noise tobe imperceptible to a human viewer. The statistics for the perceptioncriterion depend only on pixel temporal noise as follows:

${PFPN}_{required} \leq \frac{\sigma_{T}}{4}$${PFPN}_{realized} = {\frac{\sigma_{T}}{\sqrt{N_{f}}}\therefore{N_{f} \geq 16}}$

where σ_(T) is the pixel temporal noise. Therefore, the frame correctionprocess should be effective so long as there are at least 16 dark framesused to compute the average.

In an embodiment, SES capture on dark frames only is calculatedaccording to:

b_(i, j) = d_(i, j)  (j = 0)$b_{i,j} = {{\frac{1}{2^{w}}d_{i,j}} + {\frac{\left( {2^{w} - 1} \right)}{2^{w}}b_{i,{({j - 1})}}\mspace{14mu}\left( {j > 0} \right)}}$

where b_(i,j) is the dark frame correction buffer content for pixel i,following dark frame number j and d_(i,j) is the raw dark data for pixeli, taken from dark frame j. w is a tunable integer.

In an embodiment, SES is applied non-dark exposure frames according to:

x^(′)_(i) = x_(i) − b_(i) + B

where x_(i) is the raw data input for pixel i in any non-dark frame andb_(i) is the current dark frame buffer content. x′_(i) is the output andB is the black clamp target level.

FIG. 12 is a graphical representation of a modulation of the simpleexponential smoothing (SES) index after a gain change. In an embodiment,the values of w are tunable via control registers in communication withthe endoscopic system. The value of w may be automatically adjusted toensure corrections are reactive at startup, when T_(J) is changing mostdramatically, or in certain embodiments following changes in exposuretime. For example, if a large change in gain or exposure time occurs,the value of w can be lowered and then restored to a baselineincrementally from frame to frame. The incremental adjustments can varylinearly or in a roughly exponential manner as shown in FIG. 12.

FIG. 13 is a schematic diagram of a process flow 1300 for cancellationof fixed pattern noise. The process flow 1300 includes sampling at 1302the first pixel and resetting the frame buffer to zero. The process flow1300 includes determining at 1304 whether the sampled pixel is a darkpixel (may be referred to as an optical black pixel). If it isdetermined at 1304 that the sampled pixel is a dark pixel, then theprocess flow 1300 includes determining at 1306 whether the buffer forthe pixel is zero. If it is determined at 1306 that the buffer for thepixel dark pixel is zero, then the pixel value is written at 1308directly to the buffer location for the dark pixel. The next pixel issampled at 1310. If it is determined at 1306 that the buffer for thedark pixel is not equal to zero, then the buffer location for the darkpixel is read at 1314 and multiplied by

$\frac{\left( {2^{w} - 1} \right)}{2^{w}}.$

The result is added to the new pixel sample and divided by 2^(w) andthen written back to the buffer. The next pixel is sampled at 1310.

If it is determined at 1304 that the sampled pixel is not a dark pixel,then the process flow 1300 includes reading the buffer for the active(non-dark) pixel at 1312 and subtracting content from the data. Theprocess flow 1300 may further including adding constant black level ifrequired. The next pixel is sampled at 1310.

FIG. 14 illustrates a process flow 1400 to be implemented by acontroller and/or monochrome image signal processor (ISP) for generatinga video stream having RGB images with specialty data overlaid thereon.The specialty data may include, for example, hyperspectral imaging data,fluorescence imaging data, and/or laser mapping or topographical imagingdata. The image signal processor (ISP) chain may be assembled for thepurpose of generating sRGB image sequences from raw sensor data, yieldedin the presence of the G-R-G-B-LaserMapping light pulsing scheme. In theprocess flow 1400, the first stage is concerned with making corrections(see receiving data from the sensor at 1402, re-ordering at 1404, andsensor corrections at 1406 in FIG. 14) to account for any non-idealitiesin the sensor technology for which it is most appropriate to work in theraw data domain. At the next stage, multiple frames (for example, agreen frame 1408 a, a red-blue frame 1408 b, and a specialty frame 1408c) are buffered because each final frame derives data from multiple rawframes. The specialty frame 1408 c may include one or more specialtyexposure frames such as a hyperspectral exposure frame, a fluorescenceexposure frame, and/or a topology or laser mapping exposure frame. Theframe reconstruction at 1264 proceeds by sampling data from a currentframe and two buffered frames (see 1408 a, 1408 b, and/or 1408 c). Thereconstruction process results in full color frames in linear RGB colorspace that includes specialty image data. In this example, the whitebalance coefficients at 1418 and color correction matrix at 1420 areapplied before converting to YCbCr space at 1422 for subsequent edgeenhancement at 1424. After edge enhancement at 1424, images aretransformed back to linear RGB at 1426 for scaling at 1428, ifapplicable. Finally, the gamma transfer function at 1430 is applied totranslate the data into the sRGB domain at 1432.

FIG. 15 is an example of color fusion hardware 1500. The color fusionhardware 1500 stores in memory 1504 an R-G-B-G-Specialty video datastream with a memory writer 1502 and converts the video data stream to aparallel RGB+Specialty video data stream at 1505. The bit width on theinput side may be, e.g., 12 bits per color. The output width for thatexample would be at least 36 bits per pixel. Other embodiments may havedifferent initial bit widths and 3+ times that number for the outputwidth. The memory writer 1502 block takes as its input theRGBG-Specialty video stream and writes each frame to its correct framememory 1504 (the memory writer triggers off the same pulse generator(see 2510) that runs the laser light source). The memory 1504 may storeexposure frame data in a pattern such as the one illustrated, namely:Red, Green 1, Blue, Green 2, Specialty and then starts back with Redagain. The memory reader 1506 reads three frames at once to construct anRGB pixel. Each pixel is three times the bit width of an individualcolor component. The memory reader 1506 also triggers off the laserpulse generator at 2510. In an embodiment, the memory reader 1506 waitsuntil Red, Green 1 and Blue frames have been written, then proceeds toread them out in parallel while the writer continues writing Green 2,Specialty, and starts back on Red. When Red completes the reader beginsreading from Blue, Green 2, Specialty, and Red. This pattern continuesindefinitely.

FIG. 16 is a schematic diagram of a process flow 1600 for sensorcorrection processes. The process flow 1600 is an example implementationof the front end of an image signal process that has been developed inthe context of a system incorporating a minimal area image sensor. Inthe example process flow 1600, there are two digitizers on the sensorconverting the even and odd-numbered columns respectively andtransmitting serial data on two differential ports. The process flow1600 may be employed in a color and hyperspectral, fluorescence, and/orlaser mapping pulsed system as discussed herein. The process flow 1600may be employed to counteract non-idealities in CMOS image sensors suchas fixed pattern noise (FPN) and line noise. Fixed pattern noise is adispersion in the offsets of the sense elements. Typically, most of theFPN is a pixel to pixel dispersion which stems from random variations indark current from photodiode to photodiode. The systems disclosed hereinmaintain complete control of the illumination source, and this enablesdark data to be acquired and used to correct for the pixel and columnoffsets. In the illustrated example, a single frame buffer may be usedto make a running average of the whole frame without light using, e.g.,simple exponential smoothing. This dark average frame may be subtractedfrom every illuminated frame during regular operation. Line noise is astochastic temporal variation in the offsets of pixels within each row.Because line noise is temporal, the correction is computed for each lineand each frame. For this purpose, there are usually many optically blind(OB) pixels within each row in a pixel array. The OB pixels must firstbe sampled to assess the line offset before sampling the light sensitivepixels. The line offset is then subtracted during the line noisecorrection process.

The process flow 1600 includes performing top deserialization 1602 andbottom deserialization 1603. The process flow 1600 includes performingline reordering at the top port at 1604 and line reordering at thebottom port at 1605. The information may be stored in separate databases1632, 1634 or other memory devices upon the completion of linereordering. The process flow 1600 includes performing a black clampcalculation on the top ADC at 1606 and a black clamp calculation on thebottom ADC at 1607. The information exits the process flow 1600 on afirst-in-first-out (FIFO) basis. The process flow 1600 includesperforming line noise correction at the top ADC at 1608 and line noisecorrection at the bottom ADC at 1609. The process flow 1600 includesperforming full line recombination at 1610 and dark frame accumulationat 1612. The information may be stored in a database 1630 or othermemory device before fixed pattern noise (FPN) correction is performed.The process flow includes performing fixed pattern noise (FPN)correction at 1614 and pixel defect correction at 1616. The process flow1600 includes performing programmable digital gain at 1618 before avideo stream exits the process flow 1600 to be provided to a user.

Individual optical black pixels which do not behave normally may badlydegrade the quality of the black offset measurements. An approachdisclosed herein includes computing the media of a group of five pixelsfor each optical black pixel. The five pixels include the pixel inquestion and its four nearest neighbors. The final line offset estimatemay then be computed as the mean of all the medians. In an embodiment,some provisions are made to avoid losing statistics at the beginning andthe end. Such provisions include buffering the whole sample of opticalblacks and wrapping around the sample of five. Buffering necessitatespipelining the data and results in a delay equal to at least the totalnumber of optical blacks per analog to digital converter channel, perrow.

The line offset estimate for an even channel (assuming two analog todigital converters with odd-even interspersion), row# r can be computedas follows:

$L_{r,{even}} = \frac{2 \cdot {\sum_{{i = 0},2,{4\mspace{14mu}\ldots}}^{N_{OB} - 2}\mu_{i}}}{N_{OB}}$

The line offset where N_(OB) may be the total number of optical blackpixels per row and may be the median for optical black pixel i, computedthus:

μ₀ = median[x_((N_(OB) − 4)), x_((N_(OB) − 2)), x₀, x₂, x₄]μ₂ = median[x_((N_(OB) − 2)), x₀, x₂, x₄, x₆]μ₄ = median[x₀, x₂, x₄, x₆, x₈] …

μ_((N_(OB) − 2)) = median[x_((N_(OB) − 6)), x_((N_(OB) − 4)), x_((N_(OB) − 2)), x₀, x₂]

Likewise, the line offset estimate for an odd channel (assuming twoanalog to digital converters with odd-even interspersion), row# r can becomputed as follows:

$L_{r,{odd}} = \frac{2 \cdot {\sum_{{i = 1},3,{5\mspace{14mu}\ldots}}^{N_{OB} - 2}\mu_{i}}}{N_{OB}}$

where

μ₁ = median[x_((N_(OB) − 3)), x_((N_(OB) − 1)), x₁, x₃, x₅]μ₃ = median[x_((N_(OB) − 1)), x₁, x₃, x₅, x₇]μ₅ = median[x₁, x₃, x₅, x₇, x₉] …μ_((N_(OB) − 1)) = median[x_((N_(OB) − 5)), x_((N_(OB) − 3)), x_((N_(OB) − 1)), x₁, x₃]

The overall frame black level may be computed by accumulating each ofthe line offsets to compute the overall black level. In this approach,the overall black level is determined using simple exponential smoothing(SES). Simple exponential smoothing allows the rows at the end of theframe to have a greater influence on the final black estimate. This maybe desirable in certain implementations for addressing changes in blackoffset occurring on sub-frame timescales. The simple exponentialsmoothing algorithm determines a running estimate that may beincrementally adjusted each time a sample is made available. Forconvenience the sample can be divided by a binary number (2^(q)) beforebeing added to the previous estimate. The previous estimate may be firstmultiplied by (2^(q)−1)/2^(q) each time, in order to normalize theresult. High values of q result in greater statistical precision overtime in a stable scenario. Lower values of q may make the correctionmore reactive to rapid changes. q should be made available as a tunableparameter. This may be computed as follows:

k_(r) − L_(r)(r = 0)$k_{r} = {{\frac{1}{2^{q}}L_{r}} + {\frac{\left( {2^{q} - 1} \right)}{2^{q}}{k_{({r - 1})}\left( {r > 0} \right)}}}$

where k_(r) is the black level estimate after row r and L_(r) may be theline offset estimate for row r. The decision about what to do with theblack clamp digital to analog converters may be made after the final rowin the array has been added.

The black clamp algorithm at 1606, 1607 may require a target blacklevel, and this can be provided by an adjustable parameter. The blackclamp digital to analog converter on the sensor for the channel inquestion would be pushed up or down depending on whether the observedblack estimate may be above or below the target. The size of the pushcould be the smallest unit, i.e. one digital to analog converter count,provided the black offset may be close to the target. In the case thatthe black level may be a long way from the target, a larger proportionalpush could be made. The algorithm would need to know a rough calibrationof the correspondence between black clamp digital to analog convertercounts and sensor analog to digital converter counts and thedirectionality of digital to analog converter adjustments with respectto the output black level.

The line noise is corrected at 1608 and 1609. Line noise refers tostochastic, temporal variations in the offset of a horizontal row ofpixels. There may be multiple sources, but it can be considered as resetnoise arising from analog elements being reset each time a row of pixelsis read out. It may be temporal, and a new correction should be computedfor each new line per every frame. Since the amplification stage at theanalog to digital converter input may be the final analog element, theremay be good reason to suspect that the line noise appearsphenomenologically independent per analog to digital converter channel.One approach is to correct each analog to digital converter channelseparately.

It can be challenging to completely eliminate line noise because thesample of optical black pixels used for the line offset estimate may beseparate from the sample to which the correction may be applied. Thesample statistics are finite. Assuming the noise is Gaussian, thepost-correction line noise may be approximately equal to the uncertaintyin the line offset estimate arising from the pixel temporal noisepresent in the optical black pixels:

$\sigma_{L,{post}} \approx \frac{\sigma_{P}}{\sqrt{N_{OB}}}$

where σ_(L,post) is the post correction temporal line noise, Up isoptical black pixel temporal noise, and N_(OB) is the number of opticalblack pixels. The line noise correction also introduces a spatial linenoise component, mostly as a consequence of the pixel fixed patternnoise present within the optical black pixels:

${FPN}_{L,{post}} \approx \frac{{FPN}_{P}}{\sqrt{N_{OB}}}$

This artifact can be eliminated by the fixed pattern noise correctionlater in the chain. Simulations have indicated that in order fortemporal line noise to be invisible, the magnitude should be less thanapproximately 1/10 of the pixel temporal noise.

Line-noise correction application to optically sighted (clear) pixels:

x^(′)_(i) = x_(i) − L + B

where L is the line offset estimate for the current line, ported fromthe ‘Black Clamp’ module and B is the black clamp target level.

Full line recombination at 1610 includes combining the two data channels(i.e., the top data channel and the bottom data channel) into a fullline. The top and bottom data channels need to be interleaved in such away that the final clear pixel order reflects the correct order in thearray.

The fixed pattern noise correction at 1614 includes adjusting a runningoffset estimate on a per physical pixel basis. CMOS image sensors havemultiple noise sources. The magnitude and appearance of noise depends ona range of physical conditions. Pure Poisson or Gaussian temporal noisewith no coherent components (e.g. photon shot noise or source follower1/f read noise) looks as natural as noise can look. All otherperceivable noise types may degrade the image quality to a greaterextent for the same amplitude. Spatial noise (fixed pattern noise) maybe especially damaging and CMOS sensors inherently have at least twosources. CMOS image sensors experience pixel fixed pattern noise andcolumn fixed pattern noise. The pixel fixed pattern noise may be mostlydue to variations in photodiode leakage current (dark signal) from pixelto pixel (DSNU). This source may be exponentially dependent on junctiontemperature (T_(J)) and linearly dependent on exposure time. Columnfixed pattern noise may be a consequence of the readout architecture, inwhich pixels from within the same column are channeled through commonanalog readout elements.

Typically, an on-chip digital fixed pattern noise correction involvesdealing only with the column fixed pattern noise component and requiresone offset correction register per column. The precision of such acorrection might typically be 20 bits or so per column, which translatesto around 5 kB of RAM for a 1920×1080 array. One of the benefits ofmigrating the digital sensor corrections to the image signal processormay be the ready availability of RAM. This opens up the possibility of acomprehensive fixed pattern noise correction which cancels out any row,column or pixel-wise component. This may be accomplished by means ofsimple exponential smoothing (SES) in which each fresh dark frame samplemay be used to adjust a running offset estimate on a per physical pixelbasis.

The programmable digital gain 1618 may be executed by a programmabledigital amplifier. CMOS image sensors are usually equipped with digitalprogrammable gain stages with very fine increments. This may be tofacilitate auto exposure processes which typically modulate the gain andthe exposure time. The programmable digital amplifier can be used toalign the range of the sensor analog to digital converter to the rangeof the image signal processor (e.g. ×2 for 11 bit analog to digitalconverter to 12-bit image signal processor). A small amount of digitalgain may also be used to trim off the imprint of the digital line noiseand fixed pattern noise corrections which becomes apparent at the fullrange of the analog to digital converter.

A more space conservative approach involves combining large amounts ofcontrol RAM into single, long registers. In the extreme case, allparameters could be placed into a single register, requiring no addressROM. This solution may be not very practical because writing controlregisters takes time and typical video applications involve changing asmall number of operational parameters on a frame-by-frame basis. Themost practical solution may be afforded by concatenating functionallyrelated sets of parameters into a small number of long registers. Thedifference in space implied by having ten registers (requiring 4 addressbits) versus one may be negligible. In particular it makes sense thatall of the parameters which are written periodically at a high ratebelong together in an exclusive register (the frame register), in orderto keep the time required to write it to a minimum. Such parametersinclude the exposure times, gains, incremental offset adjustments andany others necessary to maintain continuous high-quality video. If thedigital data-path logic has been migrated off chip as described earlier,the black clamp voltage adjustment data also belongs in such a registersince it should be revised every frame too. In an implementation, duringthis configuration phase can registers be written and therefore thetiming of the frame register writes with respect to the overall frametiming should be carefully controlled by the camera.

Other examples of parametric register groupings could include; analogcurrents, analog voltages, pixel timing, vertical timing, sensorcommands (resets etc.) and so on. In FIG. 15, the arrangement ofregisters may be shown for a specific minimal-area sensor design. The“Command” register may be used for top level event-oriented 1-bitcommands such as chip resets and the loads for the other registers shownbelow it. A 2-wire protocol address decoder decides which shift registerto direct incoming 2-wire protocol data toward. To load the “Format”register, e.g., the external controller sends a command with the addressassociated with the Format register. This places the stream of data intothe Format-register shift register. Then in order to latch the data, afollow up command may be sent to the Command register with theparticular “load Format” bit set. It will be appreciated that aplurality of control registers may be used. The control registers may bedigital latches that may be loaded via shift registers. The shiftregisters may be arbitrary in length. In an embodiment, a majority ofthe plurality of control registers may be loaded using shift registersthat include many tens of bits. In an embodiment, a majority of theplurality of control registers may be loaded using shift registers thatinclude hundreds of bits. In an embodiment, a majority of the pluralityof control registers may be loaded using shift registers that includethousands of bits. In an embodiment, the shift registers may be loadedusing a serial, 2-wire protocol. In an embodiment, one of the shiftregisters may be dedicated to frame-to-frame parameter changes, such as,e.g., integration times and black clamp offset adjustments.

FIG. 17 is a schematic diagram of a pattern reconstruction process. Theexample pattern illustrated in FIG. 17 includes Red, Green, Blue, andSpecialty pulses of light that each last a duration of T 1. Thespecialty pulse may include one or more pulses for generating one ormore specialty exposure frames such as a hyperspectral exposure frame, afluorescence exposure frame, and/or a topology or laser mapping exposureframe. In various embodiments, the pulses of light may be of the sameduration or of differing durations. The Red, Green, Blue, and Specialtyexposure frames are combined to generate an RGB image with laser mappingdata overlaid thereon. A single image frame comprising a red exposureframe, a green exposure frame, a blue exposure frame, and a specialtyexposure frame requires a time period of 4*T1 to be generated. The timedurations shown in FIG. 17 are illustrative only and may vary fordifferent implementations. In other embodiments, different pulsingschemes may be employed. For example, embodiments may be based on thetiming of each color component or frame (T1) and the reconstructed framehaving a period twice that of the incoming color frame (2×T1). Differentframes within the sequence may have different frame periods and theaverage capture rate could be any multiple of the final frame rate.

In an embodiment, the dynamic range of the system is increased byvarying the pixel sensitivities of pixels within the pixel array of theimage sensor. Some pixels may sense reflected electromagnetic radiationat a first sensitivity level, other pixels may sense reflectedelectromagnetic radiation at a second sensitivity level, and so forth.The different pixel sensitivities may be combined to increase thedynamic range provided by the pixel configuration of the image sensor.In an embodiment, adjacent pixels are set at different sensitivitiessuch that each cycle includes data produced by pixels that are more andless sensitive with respect to each other. The dynamic range isincreased when a plurality of sensitivities are recorded in a singlecycle of the pixel array. In an embodiment, wide dynamic range can beachieved by having multiple global TX, each TX firing only on adifferent set of pixels. For example, in global mode, a global TX1signal is firing a set 1 of pixels, a global TX2 signal is firing a set2 of pixel, a global TXn signal is firing a set n of pixels, and soforth.

FIGS. 18A-18C each illustrate a light source 1800 having a plurality ofemitters. The emitters include a first emitter 1802, a second emitter1804, and a third emitter 1806. Additional emitters may be included, asdiscussed further below. The emitters 1802, 1804, and 1806 may includeone or more laser emitters that emit light having different wavelengths.For example, the first emitter 1802 may emit a wavelength that isconsistent with a blue laser, the second emitter 1804 may emit awavelength that is consistent with a green laser, and the third emitter1806 may emit a wavelength that is consistent with a red laser. Forexample, the first emitter 1802 may include one or more blue lasers, thesecond emitter 1804 may include one or more green lasers, and the thirdemitter 1806 may include one or more red lasers. The emitters 1802,1804, 1806 emit laser beams toward a collection region 1808, which maybe the location of a waveguide, lens, or other optical component forcollecting and/or providing light to a waveguide, such as the jumperwaveguide 206 or lumen waveguide 210 of FIG. 2.

In an implementation, the emitters 1802, 1804, and 1806 emithyperspectral wavelengths of electromagnetic radiation. Certainhyperspectral wavelengths may pierce through tissue and enable a medicalpractitioner to “see through” tissues in the foreground to identifychemical processes, structures, compounds, biological processes, and soforth that are located behind the tissues in the foreground. Thehyperspectral wavelengths may be specifically selected to identify aspecific disease, tissue condition, biological process, chemicalprocess, type of tissue, and so forth that is known to have a certainspectral response.

In an implementation where a patient has been administered a reagent ordye to aid in the identification of certain tissues, structures,chemical reactions, biological processes, and so forth, the emitters1802, 1804, and 1806 may emit wavelength(s) for fluorescing the reagentsor dyes. Such wavelength(s) may be determined based on the reagents ordyes administered to the patient. In such an embodiment, the emittersmay need to be highly precise for emitting desired wavelength(s) tofluoresce or activate certain reagents or dyes.

In an implementation, the emitters 1802, 1804, and 1806 emit a lasermapping pattern for mapping a topology of a scene and/or for calculatingdimensions and distances between objects in the scene. In an embodiment,the endoscopic imaging system is used in conjunction with multiple toolssuch as scalpels, retractors, forceps, and so forth. In such anembodiment, each of the emitters 1802, 1804, and 1806 may emit a lasermapping pattern such that a laser mapping pattern is projected on toeach tool individually. In such an embodiment, the laser mapping datafor each of the tools can be analyzed to identify distances between thetools and other objects in the scene.

In the embodiment of FIG. 18B, the emitters 1802, 1804, 1806 eachdeliver laser light to the collection region 1808 at different angles.The variation in angle can lead to variations where electromagneticenergy is located in an output waveguide. For example, if the lightpasses immediately into a fiber bundle (glass or plastic) at thecollection region 1808, the varying angles may cause different amountsof light to enter different fibers. For example, the angle may result inintensity variations across the collection region 1808. Furthermore,light from the different emitters may not be homogenously mixed so somefibers may receive different amounts of light of different colors.Variation in the color or intensity of light in different fibers canlead to non-optimal illumination of a scene. For example, variations indelivered light or light intensities may result at the scene andcaptured images.

In one embodiment, an intervening optical element may be placed betweena fiber bundle and the emitters 1802, 1804, 1806 to mix the differentcolors (wavelengths) of light before entry into the fibers or otherwaveguide. Example intervening optical elements include a diffuser,mixing rod, one or more lenses, or other optical components that mix thelight so that a given fiber receive a same amount of each color(wavelength). For example, each fiber in the fiber bundle may have asame color. This mixing may lead to the same color in each fiber butmay, in some embodiments, still result in different total brightnessdelivered to different fibers. In one embodiment, the interveningoptical element may also spread out or even out the light over thecollection region so that each fiber carries the same total amount oflight (e.g., the light may be spread out in a top hat profile). Adiffuser or mixing rod may lead to loss of light.

Although the collection region 1808 is represented as a physicalcomponent in FIG. 18A, the collection region 1808 may simply be a regionwhere light from the emitters 1802, 1804, and 1806 is delivered. In somecases, the collection region 1808 may include an optical component suchas a diffuser, mixing rod, lens, or any other intervening opticalcomponent between the emitters 1802, 1804, 1806 and an output waveguide.

FIG. 18C illustrates an embodiment of a light source 1800 with emitters1802, 1804, 1806 that provide light to the collection region 1808 at thesame or substantially same angle. The light is provided at an anglesubstantially perpendicular to the collection region 1808. The lightsource 1800 includes a plurality of dichroic mirrors including a firstdichroic mirror 1810, a second dichroic mirror 1812, and a thirddichroic mirror 1814. The dichroic mirrors 1810, 1812, 1814 includemirrors that reflect a first wavelength of light but transmit (or aretransparent to) a second wavelength of light. For example, the thirddichroic mirror 1814 may reflect blue laser light provided by the thirdemitter, while being transparent to the red and green light provided bythe first emitter 1802 and the second emitter 1804, respectively. Thesecond dichroic mirror 1812 may be transparent to red light from thefirst emitter 1802, but reflective to green light from the secondemitter 1804. If other colors or wavelengths are included dichroicmirrors may be selected to reflect light corresponding to at least oneemitter and be transparent to other emitters. For example, the thirddichroic mirror 1814 reflect the light form the third emitter 1806 butis to emitters “behind” it, such as the first emitter 1802 and thesecond emitter 1804. In embodiments where tens or hundreds of emittersare present, each dichroic mirror may be reflective to a correspondingemitter and emitters in front of it while being transparent to emittersbehind it. This may allow for tens or hundreds of emitters to emitelectromagnetic energy to the collection region 1808 at a substantiallysame angle.

Because the dichroic mirrors allow other wavelengths to transmit or passthrough, each of the wavelengths may arrive at the collection region1808 from a same angle and/or with the same center or focal point.Providing light from the same angle and/or same focal/center point cansignificantly improve reception and color mixing at the collectionregion 1808. For example, a specific fiber may receive the differentcolors in the same proportions they were transmitted/reflected by theemitters 1802, 1804, 1806 and mirrors 1810, 1812, 1814. Light mixing maybe significantly improved at the collection region compared to theembodiment of FIG. 18B. In one embodiment, any optical componentsdiscussed herein may be used at the collection region 1808 to collectlight prior to providing it to a fiber or fiber bundle.

FIG. 18C illustrates an embodiment of a light source 1800 with emitters1802, 1804, 1806 that also provide light to the collection region 1808at the same or substantially same angle. However, the light incident onthe collection region 1808 is offset from being perpendicular. Angle1816 indicates the angle offset from perpendicular. In one embodiment,the laser emitters 1802, 1804, 1806 may have cross sectional intensityprofiles that are Gaussian. As discussed previously, improveddistribution of light energy between fibers may be accomplished bycreating a more flat or top-hat shaped intensity profile. In oneembodiment, as the angle 1816 is increased, the intensity across thecollection region 1808 approaches a top hat profile. For example, atop-hat profile may be approximated even with a non-flat output beam byincreasing the angle 1816 until the profile is sufficiently flat. Thetop hat profile may also be accomplished using one or more lenses,diffusers, mixing rods, or any other intervening optical componentbetween the emitters 1802, 1804, 1806 and an output waveguide, fiber, orfiber optic bundle.

FIG. 19 is a schematic diagram illustrating a single optical fiber 1902outputting via a diffuser 1904 at an output. In one embodiment, theoptical fiber 1902 has a diameter of 500 microns, a numerical apertureof 0.65, and emits a light cone 1906 of about 70 or 80 degrees without adiffuser 1904. With the diffuser 1904, the light cone 1906 may have anangle of about 110 or 120 degrees. The light cone 1906 may be a majorityof where all light goes and is evenly distributed. The diffuser 1904 mayallow for more even distribution of electromagnetic energy of a sceneobserved by an image sensor.

In one embodiment, the lumen waveguide 210 includes a single plastic orglass optical fiber of about 500 microns. The plastic fiber may be lowcost, but the width may allow the fiber to carry a sufficient amount oflight to a scene, with coupling, diffusion, or other losses. Forexample, smaller fibers may not be able to carry as much light or poweras a larger fiber. The lumen waveguide 210 may include a single or aplurality of optical fibers. The lumen waveguide 210 may receive lightdirectly from the light source or via a jumper waveguide. A diffuser maybe used to broaden the light output 206 for a desired field of view ofthe image sensor 214 or other optical components.

Although three emitters are shown in FIGS. 18A-18C, emitters numberingfrom one into the hundreds or more may be used in some embodiments. Theemitters may have different wavelengths or spectrums of light that theyemit, and which may be used to contiguously cover a desired portion ofthe electromagnetic spectrum (e.g., the visible spectrum as well asinfrared and ultraviolet spectrums). The emitters may be configured toemit visible light such as red light, green light, and blue light, andmay further be configured to emit hyperspectral emissions ofelectromagnetic radiation, fluorescence excitation wavelengths forfluorescing a reagent, and/or laser mapping patterns for calculatingparameters and distances between objects in a scene.

FIG. 20 illustrates a portion of the electromagnetic spectrum 2000divided into twenty different sub-spectrums. The number of sub-spectrumsis illustrative only. In at least one embodiment, the spectrum 2000 maybe divided into hundreds of sub-spectrums, each with a small waveband.The spectrum may extend from the infrared spectrum 2002, through thevisible spectrum 2004, and into the ultraviolet spectrum 2006. Thesub-spectrums each have a waveband 2008 that covers a portion of thespectrum 2000. Each waveband may be defined by an upper wavelength and alower wavelength.

Hyperspectral imaging incudes imaging information from across theelectromagnetic spectrum 2000. A hyperspectral pulse of electromagneticradiation may include a plurality of sub-pulses spanning one or moreportions of the electromagnetic spectrum 2000 or the entirety of theelectromagnetic spectrum 2000. A hyperspectral pulse of electromagneticradiation may include a single partition of wavelengths ofelectromagnetic radiation. A resulting hyperspectral exposure frameincludes information sensed by the pixel array subsequent to ahyperspectral pulse of electromagnetic radiation. Therefore, ahyperspectral exposure frame may include data for any suitable partitionof the electromagnetic spectrum 2000 and may include multiple exposureframes for multiple partitions of the electromagnetic spectrum 2000. Inan embodiment, a hyperspectral exposure frame includes multiplehyperspectral exposure frames such that the combined hyperspectralexposure frame comprises data for the entirety of the electromagneticspectrum 2000.

In one embodiment, at least one emitter (such as a laser emitter) isincluded in a light source (such as the light sources 202, 1800) foreach sub-spectrum to provide complete and contiguous coverage of thewhole spectrum 2000. For example, a light source for providing coverageof the illustrated sub-spectrums may include at least 20 differentemitters, at least one for each sub-spectrum. In one embodiment, eachemitter covers a spectrum covering 40 nanometers. For example, oneemitter may emit light within a waveband from 500 nm to 540 nm whileanother emitter may emit light within a waveband from 540 nm to 580 nm.In another embodiment, emitters may cover other sizes of wavebands,depending on the types of emitters available or the imaging needs. Forexample, a plurality of emitters may include a first emitter that coversa waveband from 500 to 540 nm, a second emitter that covers a wavebandfrom 540 nm to 640 nm, and a third emitter that covers a waveband from640 nm to 650 nm. Each emitter may cover a different slice of theelectromagnetic spectrum ranging from far infrared, mid infrared, nearinfrared, visible light, near ultraviolet and/or extreme ultraviolet. Insome cases, a plurality of emitters of the same type or wavelength maybe included to provide sufficient output power for imaging. The numberof emitters needed for a specific waveband may depend on the sensitivityof a monochrome sensor to the waveband and/or the power outputcapability of emitters in that waveband.

The waveband widths and coverage provided by the emitters may beselected to provide any desired combination of spectrums. For example,contiguous coverage of a spectrum using very small waveband widths(e.g., 10 nm or less) may allow for highly selective hyperspectraland/or fluorescence imaging. The waveband widths may allow forselectively emitting the excitation wavelength(s) for one or moreparticular fluorescent reagents. Additionally, the waveband widths mayallow for selectively emitting certain partitions of hyperspectralelectromagnetic radiation for identifying specific structures, chemicalprocesses, tissues, biological processes, and so forth. Because thewavelengths come from emitters which can be selectively activated,extreme flexibility for fluorescing one or more specific fluorescentreagents during an examination can be achieved. Additionally, extremeflexibility for identifying one or more objects or processes by way ofhyperspectral imaging can be achieved. Thus, much more fluorescenceand/or hyperspectral information may be achieved in less time and withina single examination which would have required multiple examinations,delays because of the administration of dyes or stains, or the like.

FIG. 21 is a schematic diagram illustrating a timing diagram 2100 foremission and readout for generating an image. The solid line representsreadout (peaks 2102) and blanking periods (valleys) for capturing aseries of exposure frames 2104-2114. The series of exposure frames2104-2114 may include a repeating series of exposure frames which may beused for generating laser mapping, hyperspectral, and/or fluorescencedata that may be overlaid on an RGB video stream. In an embodiment, asingle image frame comprises information from multiple exposure frames,wherein one exposure frame includes red image data, another exposureframe includes green image data, and another exposure frame includesblue image data. Additionally, the single image frame may include one ormore of hyperspectral image data, fluorescence image data, and lasermapping data. The multiple exposure frames are combined to produce thesingle image frame. The single image frame is an RGB image withhyperspectral imaging data. The series of exposure frames include afirst exposure frame 2104, a second exposure frame 2106, a thirdexposure frame 2108, a fourth exposure frame 2110, a fifth exposureframe 2112, and an Nth exposure frame 2126.

Additionally, the hyperspectral image data, the fluorescence image data,and the laser mapping data can be used in combination to identifycritical tissues or structures and further to measure the dimensions ofthose critical tissues or structures. For example, the hyperspectralimage data may be provided to a corresponding system to identify certaincritical structures in a body such as a nerve, ureter, blood vessel,cancerous tissue, and so forth. The location and identification of thecritical structures may be received from the corresponding system andmay further be used to generate topology of the critical structuresusing the laser mapping data. For example, a corresponding systemdetermines the location of a cancerous tumor based on hyperspectralimaging data. Because the location of the cancerous tumor is known basedon the hyperspectral imaging data, the topology and distances of thecancerous tumor may then be calculated based on laser mapping data. Thisexample may also apply when a cancerous tumor or other structure isidentified based on fluorescence imaging data.

In one embodiment, each exposure frame is generated based on at leastone pulse of electromagnetic energy. The pulse of electromagnetic energyis reflected and detected by an image sensor and then read out in asubsequent readout (2102). Thus, each blanking period and readoutresults in an exposure frame for a specific spectrum of electromagneticenergy. For example, the first exposure frame 2104 may be generatedbased on a spectrum of a first one or more pulses 2116, a secondexposure frame 2106 may be generated based on a spectrum of a second oneor more pulses 2118, a third exposure frame 2108 may be generated basedon a spectrum of a third one or more pulses 2120, a fourth exposureframe 2110 may be generated based on a spectrum of a fourth one or morepulses 2122, a fifth exposure frame 2112 may be generated based on aspectrum of a fifth one or more pulses 2124, and an Nth exposure frame2126 may be generated based on a spectrum of an Nth one or more pulses2126.

The pulses 2116-2126 may include energy from a single emitter or from acombination of two or more emitters. For example, the spectrum includedin a single readout period or within the plurality of exposure frames2104-2114 may be selected for a desired examination or detection of aspecific tissue or condition. According to one embodiment, one or morepulses may include visible spectrum light for generating an RGB or blackand white image while one or more additional pulses are emitted to sensea spectral response to a fluorescence wavelength of electromagneticradiation. For example, pulse 2116 may include red light, pulse 2118 mayinclude blue light, and pulse 2120 may include green light while theremaining pulses 2122-2126 may include wavelengths and spectrums fordetecting a specific tissue type, fluorescing a reagent, and/or mappingthe topology of the scene. As a further example, pulses for a singlereadout period include a spectrum generated from multiple differentemitters (e.g., different slices of the electromagnetic spectrum) thatcan be used to detect a specific tissue type. For example, if thecombination of wavelengths results in a pixel having a value exceedingor falling below a threshold, that pixel may be classified ascorresponding to a specific type of tissue. Each frame may be used tofurther narrow the type of tissue that is present at that pixel (e.g.,and each pixel in the image) to provide a very specific classificationof the tissue and/or a state of the tissue (diseased/healthy) based on aspectral response of the tissue and/or whether a fluorescent reagent ispresent at the tissue.

The plurality of frames 2104-2114 is shown having varying lengths inreadout periods and pulses having different lengths or intensities. Theblanking period, pulse length or intensity, or the like may be selectedbased on the sensitivity of a monochromatic sensor to the specificwavelength, the power output capability of the emitter(s), and/or thecarrying capacity of the waveguide.

In one embodiment, dual image sensors may be used to obtainthree-dimensional images or video feeds. A three-dimensional examinationmay allow for improved understanding of a three-dimensional structure ofthe examined region as well as a mapping of the different tissue ormaterial types within the region.

In an example implementation, a fluorescent reagent is provided to apatient, and the fluorescent reagent is configured to adhere tocancerous cells. The fluorescent reagent is known to fluoresce whenradiated with a specific partition of electromagnetic radiation. Therelaxation wavelength of the fluorescent reagent is also known. In theexample implementation, the patient is imaged with an endoscopic imagingsystem as discussed herein. The endoscopic imaging system pulsespartitions of red, green, and blue wavelengths of light to generate anRGB video stream of the interior of the patient's body. Additionally,the endoscopic imaging system pulses the excitation wavelength ofelectromagnetic radiation for the fluorescent reagent that wasadministered to the patient. In the example, the patient has cancerouscells and the fluorescent reagent has adhered to the cancerous cells.When the endoscopic imaging system pulses the excitation wavelength forthe fluorescent reagent, the fluorescent reagent will fluoresce and emita relaxation wavelength. If the cancerous cells are present in the scenebeing imaged by the endoscopic imaging system, then the fluorescentreagent will also be present in the scene and will emit its relaxationwavelength after fluorescing due to the emission of the excitationwavelength. The endoscopic imaging system senses the relaxationwavelength of the fluorescent reagent and thereby senses the presence ofthe fluorescent reagent in the scene. Because the fluorescent reagent isknown to adhere to cancerous cells, the presence of the fluorescentreagent further indicates the presence of cancerous cells within thescene. The endoscopic imaging system thereby identifies the location ofcancerous cells within the scene. The endoscopic imaging system mayfurther emit a laser mapping pulsing scheme for generating a topology ofthe scene and calculating dimensions for objects within the scene. Thelocation of the cancerous cells (as identified by the fluorescenceimaging data) may be combined with the topology and dimensionsinformation calculated based on the laser mapping data. Therefore, theprecise location, size, dimensions, and topology of the cancerous cellsmay be identified. This information may be provided to a medicalpractitioner to aid in excising the cancerous cells. Additionally, thisinformation may be provided to a robotic surgical system to enable thesurgical system to excise the cancerous cells.

In a further example implementation, a patient is imaged with anendoscopic imaging system to identify quantitative diagnosticinformation about the patient's tissue pathology. In the example, thepatient is suspected or known to suffer from a disease that can betracked with hyperspectral imaging to observe the progression of thedisease in the patient's tissue. The endoscopic imaging system pulsespartitions of red, green, and blue wavelengths of light to generate anRGB video stream of the interior of the patient's body. Additionally,the endoscopic imaging system pulses one or more hyperspectralwavelengths of light that permit the system to “see through” sometissues and generate imaging of the tissue that is affected by thedisease. The endoscopic imaging system senses the reflectedhyperspectral electromagnetic radiation to generate hyperspectralimaging data of the diseased tissue, and thereby identifies the locationof the diseased tissue within the patient's body. The endoscopic imagingsystem may further emit a laser mapping pulsing scheme for generating atopology of the scene and calculating dimensions of objects within thescene. The location of the diseased tissue (as identified by thehyperspectral imaging data) may be combined with the topology anddimensions information that is calculated with the laser mapping data.Therefore, the precise location, size, dimensions, and topology of thediseased tissue can be identified. This information may be provided to amedical practitioner to aid in excising, imaging, or studying thediseased tissue. Additionally, this information may be provided to arobotic surgical system to enable the surgical system to excise thediseased tissue.

FIG. 22 is a schematic diagram of an imaging system 2200 having a singlecut filter. The system 2200 includes an endoscope 2206 or other suitableimaging device having a light source 2208 for use in a light deficientenvironment. The endoscope 2206 includes an image sensor 2204 and afilter 2202 for filtering out unwanted wavelengths of light or otherelectromagnetic radiation before reaching the image sensor 2204. Thelight source 2208 transmits light that may illuminate the surface 2212in a light deficient environment such as a body cavity. The light 2210is reflected off the surface 2212 and passes through the filter 2202before hitting the image sensor 2204.

The filter 2202 may be used in an implementation where a fluorescentreagent or dye has been administered. In such an embodiment, the lightsource 2208 emits the excitation wavelength for fluorescing thefluorescent reagent or dye. Commonly, the relaxation wavelength emittedby the fluorescent reagent or dye will be of a different wavelength thanthe excitation wavelength. The filter 2202 may be selected to filter outthe excitation wavelength and permit only the relaxation wavelength topass through the filter and be sensed by the image sensor 2204.

In one embodiment, the filter 2202 is configured to filter out anexcitation wavelength of electromagnetic radiation that causes a reagentor dye to fluoresce such that only the expected relaxation wavelength ofthe fluoresced reagent or dye is permitted to pass through the filter2202 and reach the image sensor 2204. In an embodiment, the filter 2202filters out at least a fluorescent reagent excitation wavelength between770 nm and 790 nm. In an embodiment, the filter 2202 filters out atleast a fluorescent reagent excitation wavelength between 795 nm and 815nm. In an embodiment, the filter 2202 filters out at least a fluorescentreagent excitation wavelength between 770 nm and 790 nm and between 795nm and 815 nm. In these embodiments, the filter 2202 filters out theexcitation wavelength of the reagent and permits only the relaxationwavelength of the fluoresced reagent to be read by the image sensor2204. The image sensor 2204 may be a wavelength-agnostic image sensorand the filter 2202 may be configured to permit the image sensor 2204 toonly receive the relaxation wavelength of the fluoresced reagent and notreceive the emitted excitation wavelength for the reagent. The datadetermined by the image sensor 2204 may then indicate a presence of acritical body structure, tissue, biological process, or chemical processas determined by a location of the reagent or dye.

The filter 2202 may further be used in an implementation where afluorescent reagent or dye has not been administered. The filter 2202may be selected to permit wavelengths corresponding to a desiredspectral response to pass through and be read by the image sensor 2204.The image sensor 2204 may be a monochromatic image sensor such thatpixels of the captured image that exceed a threshold or fall below athreshold may be characterized as corresponding to a certain spectralresponse or fluorescence emission. The spectral response or fluorescenceemission, as determined by the pixels captured by the image sensor 2204,may indicate the presence of a certain body tissue or structure, acertain condition, a certain chemical process, and so forth.

FIG. 23 is a schematic diagram of an imaging system 2300 having multiplecut filters. The system 2300 includes an endoscope 2306 or othersuitable imaging device having a light source 2308 for use in a lightdeficient environment. The endoscope 2306 includes an image sensor 2304and two filters 2302 a, 2302 b. It should be appreciated that inalternative embodiments, the system 2300 may include any number offilters, and the number of filters and the type of filters may beselected for a certain purpose e.g., for gathering imaging informationof a particular body tissue, body condition, chemical process, and soforth. The filters 2302 a, 2302 b are configured for preventing unwantedwavelengths of light or other electromagnetic radiation from beingsensed by the image sensor 2304. The filters 2302 a, 2302 b may beconfigured to filter out unwanted wavelengths from white light or otherelectromagnetic radiation that may be emitted by the light source 2308.

Further to the disclosure with respect to FIG. 22, the filters 2302 a,2302 b may be used in an implementation where a fluorescent reagent ordye has been administered. The filters 2302 a, 2302 b may be configuredfor blocking an emitted excitation wavelength for the reagent or dye andpermitting the image sensor 2304 to only read the relaxation wavelengthof the reagent or dye. Further, the filters 2302 a, 2302 b may be usedin an implementation where a fluorescent reagent or dye has not beenadministered. In such an implementation, the filters 2302 a, 2302 b maybe selected to permit wavelengths corresponding to a desired spectralresponse to pass through and be read by the image sensor 2304.

The multiple filters 2302 a, 2302 b may each be configured for filteringout a different range of wavelengths of the electromagnetic spectrum.For example, one filter may be configured for filtering out wavelengthslonger than a desired wavelength range and the additional filter may beconfigured for filtering out wavelengths shorter than the desiredwavelength range. The combination of the two or more filters may resultin only a certain wavelength or band of wavelengths being read by theimage sensor 2304.

In an embodiment, the filters 2302 a, 2302 b are customized such thatelectromagnetic radiation between 513 nm and 545 nm contacts the imagesensor 2304. In an embodiment, the filters 2302 a, 2302 b are customizedsuch that electromagnetic radiation between 565 nm and 585 nm contactsthe image sensor 2304. In an embodiment, the filters 2302 a, 2302 b arecustomized such that electromagnetic radiation between 900 nm and 1000nm contacts the image sensor 2304. In an embodiment, the filters 2302 a,2302 b are customized such that electromagnetic radiation between 425 nmand 475 nm contacts the image sensor 2304. In an embodiment, the filters2302 a, 2302 b are customized such that electromagnetic radiationbetween 520 nm and 545 nm contacts the image sensor 2304. In anembodiment, the filters 2302 a, 2302 b are customized such thatelectromagnetic radiation between 625 nm and 645 nm contacts the imagesensor 2304. In an embodiment, the filters 2302 a, 2302 b are customizedsuch that electromagnetic radiation between 760 nm and 795 nm contactsthe image sensor 2304. In an embodiment, the filters 2302 a, 2302 b arecustomized such that electromagnetic radiation between 795 nm and 815 nmcontacts the image sensor 2304. In an embodiment, the filters 2302 a,2302 b are customized such that electromagnetic radiation between 370 nmand 420 nm contacts the image sensor 2304. In an embodiment, the filters2302 a, 2302 b are customized such that electromagnetic radiationbetween 600 nm and 670 nm contacts the image sensor 2304. In anembodiment, the filters 2302 a, 2302 b are configured for permittingonly a certain fluorescence relaxation emission to pass through thefilters 2302 a, 2302 b and contact the image sensor 2304.

In an embodiment, the system 2300 includes multiple image sensors 2304and may particularly include two image sensors for use in generating athree-dimensional image. The image sensor(s) 2304 may becolor/wavelength agnostic and configured for reading any wavelength ofelectromagnetic radiation that is reflected off the surface 2312. In anembodiment, the image sensors 2304 are each color dependent orwavelength dependent and configured for reading electromagneticradiation of a particular wavelength that is reflected off the surface2312 and back to the image sensors 2304. Alternatively, the image sensor2304 may include a single image sensor with a plurality of differentpixel sensors configured for reading different wavelengths or colors oflight, such as a Bayer filter color filter array. Alternatively, theimage sensor 2304 may include one or more color agnostic image sensorsthat may be configured for reading different wavelengths ofelectromagnetic radiation according to a pulsing schedule such as thoseillustrated in FIGS. 5-7E, for example.

FIG. 24 is a schematic diagram illustrating a system 2400 for mapping asurface and/or tracking an object in a light deficient environmentthrough laser mapping imaging. In an embodiment, an endoscope 2406 in alight deficient environment pulses a grid array 2406 (may be referred toas a laser map pattern) on a surface 2404. The grid array 2406 includesvertical hashing 2408 and horizontal hashing 2410 in one embodiment asillustrated in FIG. 24. It should be appreciated the grid array 2406 mayinclude any suitable array for mapping a surface 2404, including, forexample, a raster grid of discrete points, an occupancy grid map, a dotarray, and so forth. Additionally, the endoscope 2406 may pulse multiplegrid arrays 2406 and may, for example, pulse one or more individual gridarrays on each of a plurality of objects or structures within the lightdeficient environment.

In an embodiment, the system 2400 pulses a grid array 2406 that may beused for mapping a three-dimensional topology of a surface and/ortracking a location of an object such as a tool or another device in alight deficient environment. In an embodiment, the system 2400 providesdata to a third-party system or computer algorithm for determiningsurface dimensions and configurations by way of light detection andranging (LIDAR) mapping. The system 2400 may pulse any suitablewavelength of light or electromagnetic radiation in the grid array 2406,including, for example, ultraviolet light, visible, light, and/orinfrared or near infrared light. The surface 2404 and/or objects withinthe environment may be mapped and tracked at very high resolution andwith very high accuracy and precision.

In an embodiment, the system 2400 includes an imaging device having atube, one or more image sensors, and a lens assembly having an opticalelement corresponding to the one or more image sensors. The system 2400may include a light engine having an emitter generating one or morepulses of electromagnetic radiation and a lumen transmitting the one ormore pulses of electromagnetic radiation to a distal tip of an endoscopewithin a light deficient environment such as a body cavity. In anembodiment, at least a portion of the one or more pulses ofelectromagnetic radiation includes a laser map pattern that is emittedonto a surface within the light deficient environment, such as a surfaceof body tissue and/or a surface of tools or other devices within thebody cavity. The endoscope 2406 may include a two-dimensional,three-dimensional, or n-dimensional camera for mapping and/or trackingthe surface, dimensions, and configurations within the light deficientenvironment.

In an embodiment, the system 2400 includes a processor for determining adistance of an endoscope or tool from an object such as the surface2404. The processor may further determine an angle between the endoscopeor tool and the object. The processor may further determine surface areainformation about the object, including for example, the size ofsurgical tools, the size of structures, the size of anatomicalstructures, location information, and other positional data and metrics.The system 2400 may include one or more image sensors that provide imagedata that is output to a control system for determining a distance of anendoscope or tool to an object such as the surface 2404. The imagesensors may output information to a control system for determining anangle between the endoscope or tool to the object. Additionally, theimage sensors may output information to a control system for determiningsurface area information about the object, the size of surgical tools,size of structures, size of anatomical structures, location information,and other positional data and metrics.

In an embodiment, the grid array 2406 is pulsed by an emitter of theendoscope 2406 at a sufficient speed such that the grid array 2406 isnot visible to a user. In various implementations, it may be distractingto a user to see the grid array 2406 during an endoscopic imagingprocedure and/or endoscopic surgical procedure. The grid array 2406 maybe pulsed for sufficiently brief periods such that the grid array 2406cannot be detected by a human eye. In an alternative embodiment, theendoscope 2406 pulses the grid array 2406 at a sufficient recurringfrequency such that the grid array 2406 may be viewed by a user. In suchan embodiment, the grid array 2406 may be overlaid on an image of thesurface 2404 on a display. The grid array 2406 may be overlaid on ablack-and-white or RGB image of the surface 2404 such that the gridarray 2406 may be visible by a user during use of the system 2400. Auser of the system 2400 may indicate whether the grid array 2406 shouldbe overlaid on an image of the surface 2404 and/or whether the gridarray 2406 should be visible to the user. The system 2400 may include adisplay that provides real-time measurements of a distance from theendoscope 2406 to the surface 2404 or another object within the lightdeficient environment. The display may further provide real-time surfacearea information about the surface 2404 and/or any objects, structures,or tools within the light deficient environment. The accuracy of themeasurements may be accurate to less than one millimeter.

In an embodiment, the system 2400 pulses a plurality of grid arrays2406. In an embodiment, each of the plurality of grid arrays 2406corresponds to a tool or other device present within the light deficientenvironment. The precise locations and parameters of each of the toolsand other devices may be tracked by pulsing and sensing the plurality ofgrid arrays 2406. The information generated by sensing the reflectedgrid arrays 2406 can be assessed to identify relative locations of thetools and other devices within the light deficient environment.

The endoscope 2406 may pulse electromagnetic radiation according to apulsing schedule such as those illustrated herein that may furtherinclude pulsing of the grid array 2406 along with pulsing Red, Green,and Blue light for generating an RGB image and further generating a gridarray 2406 that may be overlaid on the RGB image and/or used for mappingand tracking the surface 2404 and objects within the light deficientenvironment. The grid array 2406 may additionally be pulsed inconjunction with hyperspectral or fluorescent excitation wavelengths ofelectromagnetic radiation. The data from each of the RGB imaging, thelaser mapping imaging, the hyperspectral imaging, and the fluorescenceimaging may be combined to identify the locations, dimensions, andsurface topology of critical structures in a body.

In an embodiment, the endoscope 2406 includes one or more color agnosticimage sensors. In an embodiment, the endoscope 2406 includes two coloragnostic image sensors for generating a three-dimensional image or mapof the light deficient environment. The image sensors may generate anRGB image of the light deficient environment according to a pulsingschedule as disclosed herein. Additionally, the image sensors maydetermine data for mapping the light deficient environment and trackingone or more objects within the light deficient environment based on datadetermined when the grid array 2406 is pulsed. Additionally, the imagesensors may determine spectral or hyperspectral data along withfluorescence imaging data according to a pulsing schedule that may bemodified by a user to suit the particular needs of an imaging procedure.In an embodiment, a pulsing schedule includes Red, Green, and Bluepulses along with pulsing of a grid array 2406 and/or pulsing forgenerating hyperspectral image data and/or fluorescence image data. Invarious implementations, the pulsing schedule may include any suitablecombination of pulses of electromagnetic radiation according to theneeds of a user. The recurring frequency of the different wavelengths ofelectromagnetic radiation may be determined based on, for example, theenergy of a certain pulse, the needs of the user, whether certain data(for example, hyperspectral data and/or fluorescence imaging data) needsto be continuously updated or may be updated less frequently, and soforth.

The pulsing schedule may be modified in any suitable manner, and certainpulses of electromagnetic radiation may be repeated at any suitablefrequency, according to the needs of a user or computer-implementedprogram for a certain imaging procedure. For example, in an embodimentwhere surface tracking data generated based on the grid array 2406 isprovided to a computer-implemented program for use in, for example, arobotic surgical procedure, the grid array 2406 may be pulsed morefrequently than if the surface tracking data is provided to a user whois visualizing the scene during the imaging procedure. In such anembodiment where the surface tracking data is used for a roboticsurgical procedure, the surface tracking data may need to be updatedmore frequently or may need to be exceedingly accurate such that thecomputer-implemented program may execute the robotic surgical procedurewith precision and accuracy.

In an embodiment, the system 2400 is configured to generate an occupancygrid map comprising an array of cells divided into grids. The system2400 is configured to store height values for each of the respectivegrid cells to determine a surface mapping of a three-dimensionalenvironment in a light deficient environment.

FIGS. 25A and 25B illustrate a perspective view and a side view,respectively, of an implementation of a monolithic sensor 2500 having aplurality of pixel arrays for producing a three-dimensional image inaccordance with the teachings and principles of the disclosure. Such animplementation may be desirable for three-dimensional image capture,wherein the two-pixel arrays 2502 and 2504 may be offset during use. Inanother implementation, a first pixel array 2502 and a second pixelarray 2504 may be dedicated to receiving a predetermined range of wavelengths of electromagnetic radiation, wherein the first pixel array isdedicated to a different range of wavelength electromagnetic radiationthan the second pixel array.

FIGS. 26A and 26B illustrate a perspective view and a side view,respectively, of an implementation of an imaging sensor 2600 built on aplurality of substrates. As illustrated, a plurality of pixel columns2604 forming the pixel array are located on the first substrate 2602 anda plurality of circuit columns 2608 are located on a second substrate2606. Also illustrated in the figure are the electrical connection andcommunication between one column of pixels to its associated orcorresponding column of circuitry. In one implementation, an imagesensor, which might otherwise be manufactured with its pixel array andsupporting circuitry on a single, monolithic substrate/chip, may havethe pixel array separated from all or a majority of the supportingcircuitry. The disclosure may use at least two substrates/chips, whichwill be stacked together using three-dimensional stacking technology.The first 2602 of the two substrates/chips may be processed using animage CMOS process. The first substrate/chip 2602 may be comprisedeither of a pixel array exclusively or a pixel array surrounded bylimited circuitry. The second or subsequent substrate/chip 2606 may beprocessed using any process and does not have to be from an image CMOSprocess. The second substrate/chip 2606 may be, but is not limited to, ahighly dense digital process to integrate a variety and number offunctions in a very limited space or area on the substrate/chip, or amixed-mode or analog process to integrate for example precise analogfunctions, or a RF process to implement wireless capability, or MEMS(Micro-Electro-Mechanical Systems) to integrate MEMS devices. The imageCMOS substrate/chip 2602 may be stacked with the second or subsequentsubstrate/chip 2606 using any three-dimensional technique. The secondsubstrate/chip 2606 may support most, or a majority, of the circuitrythat would have otherwise been implemented in the first image CMOS chip2602 (if implemented on a monolithic substrate/chip) as peripheralcircuits and therefore have increased the overall system area whilekeeping the pixel array size constant and optimized to the fullestextent possible. The electrical connection between the twosubstrates/chips may be done through interconnects, which may be wirebonds, bump and/or TSV (Through Silicon Via).

FIGS. 27A and 27B illustrate a perspective view and a side view,respectively, of an implementation of an imaging sensor 2700 having aplurality of pixel arrays for producing a three-dimensional image. Thethree-dimensional image sensor may be built on a plurality of substratesand may comprise the plurality of pixel arrays and other associatedcircuitry, wherein a plurality of pixel columns 2704 a forming the firstpixel array and a plurality of pixel columns 2704 b forming a secondpixel array are located on respective substrates 2702 a and 2702 b,respectively, and a plurality of circuit columns 2408 a and 2408 b arelocated on a separate substrate 2406. Also illustrated are theelectrical connections and communications between columns of pixels toassociated or corresponding column of circuitry.

The plurality of pixel arrays may sense information simultaneously andthe information from the plurality of pixel arrays may be combined togenerate a three-dimensional image. In an embodiment, an endoscopicimaging system includes two or more pixel arrays that can be deployed togenerate three-dimensional imaging. The endoscopic imaging system mayinclude an emitter for emitting pulses of electromagnetic radiationduring a blanking period of the pixel arrays. The pixel arrays may besynced such that the optical black pixels are read (i.e., the blankingperiod occurs) at the same time for the two or more pixel arrays. Theemitter may emit pulses of electromagnetic radiation for charging eachof the two or more pixel arrays. The two or more pixel arrays may readtheir respective charged pixels at the same time such that the readoutperiods for the two or more pixel arrays occur at the same time or atapproximately the same time. In an embodiment, the endoscopic imagingsystem includes multiple emitters that are each individual synced withone or more pixel arrays of a plurality of pixel arrays. Informationfrom a plurality of pixel arrays may be combined to generatethree-dimensional image frames and video streams.

It will be appreciated that the teachings and principles of thedisclosure may be used in a reusable device platform, a limited usedevice platform, a re-posable use device platform, or a singleuse/disposable device platform without departing from the scope of thedisclosure. It will be appreciated that in a re-usable device platforman end-user is responsible for cleaning and sterilization of the device.In a limited use device platform, the device can be used for somespecified amount of times before becoming inoperable. Typical new deviceis delivered sterile with additional uses requiring the end-user toclean and sterilize before additional uses. In a re-posable use deviceplatform, a third-party may reprocess the device (e.g., cleans, packagesand sterilizes) a single-use device for additional uses at a lower costthan a new unit. In a single use/disposable device platform a device isprovided sterile to the operating room and used only once before beingdisposed of.

Examples

The following examples pertain to preferred features of furtherembodiments:

Example 1 is a method. The method includes actuating an emitter to emita plurality of pulses of electromagnetic radiation and sensing reflectedelectromagnetic radiation resulting from the plurality of pulses ofelectromagnetic radiation with a pixel array of an image sensor togenerate a plurality of exposure frames. The method includes generatinga reference frame for use in removing fixed pattern noise from theplurality of exposure frames, wherein the reference frame is based ondark frame data captured when the emitter is not emittingelectromagnetic radiation. The method includes reducing fixed patternnoise in an exposure frame of the plurality of exposure frames bysubtracting the reference frame from the exposure frame. The method issuch that at least a portion of the pulses of electromagnetic radiationemitted by the emitter comprises one or more of: electromagneticradiation having a wavelength from about 513 nm to about 545 nm;electromagnetic radiation having a wavelength from about 565 nm to about585 nm; electromagnetic radiation having a wavelength from about 900 nmto about 1000 nm; an excitation wavelength of electromagnetic radiationthat causes a reagent to fluoresce; or a laser mapping pattern.

Example 2 is a method as in Example 1, further comprising: stopping theemitter from pulsing electromagnetic radiation; and sensing the darkframe data with the pixel array when the emitter is not emittingelectromagnetic radiation.

Example 3 is a method as in any of Examples 1-2, wherein the pluralityof pulses of electromagnetic radiation are emitted in a pattern ofvarying wavelengths of electromagnetic radiation, and wherein theemitter repeats the pattern of varying wavelengths of electromagneticradiation.

Example 4 is a method as in any of Examples 1-3, wherein the pattern ofvarying wavelengths of electromagnetic radiation comprises azero-emission period wherein the emitter does not pulse electromagneticradiation, and wherein the method further comprises sensing the darkframe data with the pixel array during the zero-emission period.

Example 5 is a method as in any of Examples 1-4, further comprisingsensing a plurality of dark exposure frames with the pixel array whenthe emitter is not emitting electromagnetic radiation, wherein each ofthe plurality of dark exposure frames comprises dark frame data.

Example 6 is a method as in any of Examples 1-5, wherein the pluralityof dark exposure frames are interspersed within the plurality ofexposure frames.

Example 7 is a method as in any of Examples 1-6, wherein generating thereference frame comprises generating a plurality of reference framesbased on the plurality of dark exposure frames, and wherein the methodfurther comprises enhancing precision of at least one reference frame ofthe plurality of reference frames by sampling subsequent dark frame datafrom subsequent dark exposure frames.

Example 8 is a method as in any of Examples 1-7, wherein enhancingprecision of the at least one reference frame comprises accounting forthe subsequent dark frame data from the subsequent dark exposure framesusing exponential smoothing.

Example 9 is a method as in any of Examples 1-8, wherein generating thereference frame comprises interpolating two or more instances of darkframe data from two or more dark exposure frames captured at differentintegration times.

Example 10 is a method as in any of Examples 1-9, wherein sensing thereflected electromagnetic radiation comprises sensing during a readoutperiod of the pixel array, wherein the readout period is a duration oftime when active pixels in the pixel array are read.

Example 11 is a method as in any of Examples 1-10, wherein actuating theemitter comprises actuating the emitter to emit, during a pulseduration, a plurality of sub-pulses of electromagnetic radiation havinga sub-duration shorter than the pulse duration.

Example 12 is a method as in any of Examples 1-11, wherein actuating theemitter comprises actuating the emitter to emit two or more wavelengthssimultaneously as a single pulse or a single sub-pulse.

Example 13 is a method as in any of Examples 1-12, wherein sensing thereflected electromagnetic radiation comprises generating a fluorescenceexposure frame, and wherein the method further comprises providing thefluorescence exposure frame to a corresponding fluorescence system thatdetermines a location of a critical tissue structure within a scenebased on the fluorescence exposure frame.

Example 14 is a method as in any of Examples 1-13, further comprising:the location of the critical tissue structure from the correspondingfluorescence system; generating an overlay frame comprising the locationof the critical tissue structure; and combining the overlay frame with acolor image frame depicting the scene to indicate the location of thecritical tissue structure within the scene.

Example 15 is a method as in any of Examples 1-14, wherein sensingreflected electromagnetic by the pixel array comprises sensing reflectedelectromagnetic radiation resulting from the laser mapping pattern togenerate a laser mapping exposure frame, and wherein the method furthercomprises: providing the laser mapping exposure frame to a correspondinglaser mapping system that determines a topology of the scene and/ordimensions of one or more objects within the scene; providing thelocation of the critical tissue structure to the corresponding lasermapping system; and receiving a topology and/or dimension of thecritical tissue structure from the corresponding laser mapping system.

Example 16 is a method as in any of Examples 1-15, wherein the criticaltissue structure comprises one or more of a nerve, a ureter, a bloodvessel, an artery, a blood flow, or a tumor.

Example 17 is a method as in any of Examples 1-16, further comprisingsynchronizing timing of the plurality of pulses of electromagneticradiation to be emitted during a blanking period of the image sensor,wherein the blanking period corresponds to a time between a readout of alast row of active pixels in the pixel array and a beginning of a nextsubsequent readout of active pixels in the pixel array.

Example 18 is a method as in any of Examples 1-17, wherein sensing thereflected electromagnetic radiation comprises sensing with a first pixelarray and a second pixel array such that a three-dimensional image canbe generated based on the sensed reflected electromagnetic radiation.

Example 19 is a method as in any of Examples 1-18, wherein actuating theemitter comprises actuating the emitter to emit a sequence of pulses ofelectromagnetic radiation repeatedly sufficient for generating a videostream comprising a plurality of image frames, wherein each image framein the video stream comprises data from a plurality of exposure frames,and wherein each of the exposure frames corresponds to a pulse ofelectromagnetic radiation.

Example 20 is a method as in any of Examples 1-19, wherein at least aportion of the plurality of pulses of electromagnetic radiation emittedby the emitter is an excitation wavelength for fluorescing a reagent,and wherein at least a portion of the reflected electromagneticradiation sensed by the pixel array is a relaxation wavelength of thereagent.

Example 21 is a method as in any of Examples 1-20, wherein sensingreflected electromagnetic radiation by the pixel array comprisesgenerating a laser mapping exposure frame by sensing reflectedelectromagnetic radiation resulting from the emitter pulsing the lasermapping pattern, wherein the laser mapping exposure frame comprisesinformation for determining real time measurements comprising one ormore of: a distance from an endoscope to an object; an angle between anendoscope and the object; or surface topology information about theobject.

Example 22 is a method as in any of Examples 1-21, wherein the lasermapping exposure frame comprises information for determining the realtime measurements to an accuracy of less than 10 centimeters.

Example 23 is a method as in any of Examples 1-22, wherein the lasermapping exposure frame comprises information for determining the realtime measurements to an accuracy of less than one millimeter.

Example 24 is a method as in any of Examples 1-23, wherein actuating theemitter to emit the plurality of pulses of electromagnetic radiationcomprises actuating the emitter to emit a plurality of tool-specificlaser mapping patterns for each of a plurality of tools within a scene.

Example 25 is a method as in any of Examples 1-24, wherein the lasermapping pattern emitted by the emitter comprises a first output and asecond output that are independent from one another, wherein the firstoutput is for light illumination and the second output is for tooltracking.

Example 26 is a method as in any of Examples 1-25, wherein at least aportion of the plurality of pulses of electromagnetic radiation comprisea hyperspectral emission comprising one of: electromagnetic radiationhaving a wavelength from about 513 nm to about 545 nm andelectromagnetic radiation having a wavelength from about 900 nm to about1000 nm; or electromagnetic radiation having a wavelength from about 565nm to about 585 nm and electromagnetic radiation having a wavelengthfrom about 900 nm to about 1000 nm; wherein sensing reflectedelectromagnetic radiation by the pixel array comprises generating ahyperspectral exposure frame based on the hyperspectral emission.

Example 27 is a method as in any of Examples 1-26, further comprising:providing the hyperspectral exposure frame to a correspondinghyperspectral system that determines a location of a critical tissuestructure based on the hyperspectral exposure frame; receiving thelocation of the critical tissue structure from the correspondinghyperspectral system; generating an overlay frame comprising thelocation of the critical tissue structure; and combining the overlayframe with a color image frame depicting the scene to indicate thelocation of the critical tissue structure within the scene.

Example 28 is a method as in any of Examples 1-27, wherein sensingreflected electromagnetic radiation by the pixel array comprisesgenerating a laser mapping exposure frame based on emission of the lasermapping pattern, and wherein the method further comprises: providing thelaser mapping exposure frame to a corresponding laser mapping systemthat determines a topology of the scene and/or dimensions of one or moreobjects within the scene; providing the location of the critical tissuestructure to the corresponding laser mapping system; and receiving atopology and/or dimension of the critical tissue structure from thecorresponding laser mapping system.

Example 29 is a method as in any of Examples 1-28, wherein the criticaltissue structure is one or more of a nerve, a ureter, a blood vessel, anartery, a blood flow, cancerous tissue, or a tumor.

Example 30 is a system. The system includes an emitter for emitting aplurality of pulses of electromagnetic radiation and an image sensorcomprising a pixel array for sensing reflected electromagnetic radiationto generate a plurality of exposure frames. The system includes one ormore processors configurable to execute instructions stored innon-transitory computer readable storage media. The instructionsincludes generating a reference frame for use in removing fixed patternnoise from the plurality of exposure frames, wherein the reference frameis based on dark frame data. The instructions includes reducing fixedpattern noise in an exposure frame of the plurality of exposure framesby subtracting the reference frame from the exposure frame. The systemis such that at least a portion of the pulses of electromagneticradiation emitted by the emitter comprises one or more of:electromagnetic radiation having a wavelength from about 513 nm to about545 nm; electromagnetic radiation having a wavelength from about 565 nmto about 585 nm; electromagnetic radiation having a wavelength fromabout 900 nm to about 1000 nm; an excitation wavelength ofelectromagnetic radiation that causes a reagent to fluoresce; or a lasermapping pattern.

Example 31 is a system as in Example 30, wherein the instructionsfurther comprise: stopping the emitter from pulsing electromagneticradiation; and sensing the dark frame data with the pixel array when theemitter is not emitting electromagnetic radiation.

Example 32 is a system as in any of Examples 30-31, wherein theplurality of pulses of electromagnetic radiation are emitted in apattern of varying wavelengths of electromagnetic radiation, and whereinthe emitter repeats the pattern of varying wavelengths ofelectromagnetic radiation.

Example 33 is a system as in any of Examples 30-32, wherein the patternof varying wavelengths of electromagnetic radiation comprises azero-emission period wherein the emitter does not pulse electromagneticradiation, and wherein the method further comprises sensing the darkframe data with the pixel array during the zero-emission period.

Example 34 is a system as in any of Examples 30-33, wherein the pixelarray senses a plurality of dark exposure frames over a plurality ofinstances when the emitter is not emitting electromagnetic radiation,wherein each of the plurality of dark exposure frames comprises darkframe data.

Example 35 is a system as in any of Examples 30-34, wherein at least aportion of the pulses of electromagnetic radiation emitted by theemitter results in a fluorescence exposure frame created by the imagesensor, and wherein the instructions further comprise providing thefluorescence exposure frame to a corresponding fluorescence system thatdetermines a location of a critical tissue structure within a scenebased on the fluorescence exposure frame.

Example 36 is a system as in any of Examples 30-35, wherein theinstructions further comprise: receiving the location of the criticaltissue structure from the corresponding fluorescence system; generatingan overlay frame comprising the location of the critical tissuestructure; and combining the overlay frame with a color image framedepicting the scene to indicate the location of the critical tissuestructure within the scene.

Example 37 is a system as in any of Examples 30-36, wherein sensingreflected electromagnetic by the pixel array comprises sensing reflectedelectromagnetic radiation resulting from the laser mapping pattern togenerate a laser mapping exposure frame, and wherein the instructionsfurther comprise: providing the laser mapping exposure frame to acorresponding laser mapping system that determines a topology of thescene and/or dimensions of one or more objects within the scene; providethe location of the critical tissue structure to the corresponding lasermapping system; and receive a topology and/or dimension of the criticaltissue structure from the corresponding laser mapping system.

Example 38 is a means for performing any of the methods depicted inExamples 1-29.

It will be appreciated that various features disclosed herein providesignificant advantages and advancements in the art. The following claimsare exemplary of some of those features.

In the foregoing Detailed Description of the Disclosure, variousfeatures of the disclosure are grouped together in a single embodimentfor the purpose of streamlining the disclosure. This method ofdisclosure is not to be interpreted as reflecting an intention that theclaimed disclosure requires more features than are expressly recited ineach claim. Rather, inventive aspects lie in less than all features of asingle foregoing disclosed embodiment.

It is to be understood that any features of the above-describedarrangements, examples, and embodiments may be combined in a singleembodiment comprising a combination of features taken from any of thedisclosed arrangements, examples, and embodiments.

It is to be understood that the above-described arrangements are onlyillustrative of the application of the principles of the disclosure.Numerous modifications and alternative arrangements may be devised bythose skilled in the art without departing from the spirit and scope ofthe disclosure and the appended claims are intended to cover suchmodifications and arrangements.

Thus, while the disclosure has been shown in the drawings and describedabove with particularity and detail, it will be apparent to those ofordinary skill in the art that numerous modifications, including, butnot limited to, variations in size, materials, shape, form, function andmanner of operation, assembly and use may be made without departing fromthe principles and concepts set forth herein.

Further, where appropriate, functions described herein can be performedin one or more of: hardware, software, firmware, digital components, oranalog components. For example, one or more application specificintegrated circuits (ASICs) or field programmable gate arrays (FPGAs)can be programmed to carry out one or more of the systems and proceduresdescribed herein. Certain terms are used throughout the followingdescription and claims to refer to particular system components. As oneskilled in the art will appreciate, components may be referred to bydifferent names. This document does not intend to distinguish betweencomponents that differ in name, but not function.

The foregoing description has been presented for the purposes ofillustration and description. It is not intended to be exhaustive or tolimit the disclosure to the precise form disclosed. Many modificationsand variations are possible in light of the above teaching. Further, itshould be noted that any or all the aforementioned alternateimplementations may be used in any combination desired to formadditional hybrid implementations of the disclosure.

Further, although specific implementations of the disclosure have beendescribed and illustrated, the disclosure is not to be limited to thespecific forms or arrangements of parts so described and illustrated.The scope of the disclosure is to be defined by the claims appendedhereto, any future claims submitted here and in different applications,and their equivalents.

1-30. (canceled)
 31. A system comprising: an emitter comprising aplurality of electromagnetic sources for emitting electromagneticradiation; an image sensor for sensing reflected electromagneticradiation; and a processor for executing instructions stored innon-transitory computer readable storage medium, the instructionscomprising: receiving an exposure frame sensed by the image sensor;generating a reference frame based on dark frame data, wherein the darkframe data is read out by the image sensor when the emitter is notemitting electromagnetic radiation; and subtracting the reference framefrom the exposure frame; wherein the plurality of electromagneticsources of the emitter comprises one or more of: a laser mapping sourcefor emitting electromagnetic radiation in a laser mapping pattern; amultispectral source for emitting a multispectral wavelength ofelectromagnetic radiation; or a fluorescence source for emitting afluorescence excitation wavelength of electromagnetic radiation.
 32. Thesystem of claim 31, wherein the instructions are such that generatingthe reference frame comprises: receiving a plurality of dark exposureframes sensed by the image sensor, wherein each of the plurality of darkexposure frames comprises dark frame data; and applying simpleexponential smoothing to the plurality of dark exposure frames such thatolder darks exposure frames have lesser weight than newer dark exposureframes.
 33. The system of claim 31, wherein the emitter pulses aplurality of pulses of electromagnetic radiation in a pattern, andwherein the pattern comprises a visible pulse comprising a visiblewavelength of electromagnetic radiation and further comprises a pulse ofa laser mapping pattern emitted by the laser mapping source; and one ormore of a multispectral pulse emitted by the multispectral source, or afluorescence pulse emitted by the fluorescence source.
 34. The system ofclaim 31, wherein the multispectral wavelength of electromagneticradiation comprises one or more of: electromagnetic radiation comprisinga wavelength within a range from about 513 nm to about 545 nm;electromagnetic radiation comprising a wavelength within a range fromabout 565 nm to about 585 nm; or electromagnetic radiation comprising awavelength within a range from about 900 nm to about 1000 nm.
 35. Thesystem of claim 31, wherein the fluorescence excitation wavelength ofelectromagnetic radiation comprises one or more of: electromagneticradiation comprising a wavelength within a range from about 770 nm toabout 795 nm; or electromagnetic radiation comprising a wavelengthwithin a range from about 790 nm to about 815 nm.
 36. The system ofclaim 31, wherein the image sensor senses a laser mapping frame inresponse to an emission by the laser mapping source, and wherein thelaser mapping frame comprises data for calculating one or more of athree-dimensional topography of a scene, a dimension of one or moreobjects within a scene, or a distance.
 37. The system of claim 31,wherein the electromagnetic radiation in the laser mapping patterncomprises one or more of a raster grid of discrete points, an occupancygrid map, a dot array, vertical hashing, or horizontal hashing.
 38. Thesystem of claim 31, further comprising a controller in communicationwith the emitter and the image sensor, wherein the controllersynchronizes the emitter and the image sensor such that the image sensorsenses a frame in response to the emitter pulsing an emission ofelectromagnetic radiation.
 39. The system of claim 31, furthercomprising a controller in communication with the emitter and the imagesensor, wherein the controller is configured to receive frame datasensed by the image sensor, wherein the frame data comprises: a colorimage frame sensed in response to an emission by a visible source,wherein the visible source is configured to emit a visible wavelength ofelectromagnetic radiation; a laser mapping frame sensed in response toan emission by the laser mapping source; a fluorescence frame sensed inresponse to an emission by the fluorescence source; and a multispectralframe sensed in response to an emission by the multispectral source. 40.The system of claim 31, wherein the image sensor senses a fluorescenceframe in response to the emitter pulsing the fluorescence excitationwavelength of electromagnetic radiation, and wherein a pixel array ofthe image sensor senses a fluorescence relaxation wavelength to generatethe fluorescence frame.
 41. The system of claim 40, wherein thefluorescence relaxation wavelength is released by a reagent thatfluoresces in response to an emission of the fluorescence excitationwavelength of electromagnetic radiation.
 42. The system of claim 41,wherein the reagent binds to a tissue structure within a scene, andwherein the fluorescence frame comprises data indicating a location ofthe tissue structure within the scene.
 43. The system of claim 42,further comprising a controller configured to provide the fluorescenceframe to a corresponding fluorescence system configured to identify thelocation of the tissue structure within the scene based on thefluorescence frame.
 44. The system of claim 43, wherein the controlleris further configured to provide a laser mapping frame to acorresponding laser mapping system, wherein the laser mapping frame issensed by the image sensor in response to the emitter pulsing theelectromagnetic radiation in the laser mapping pattern, and wherein thecorresponding laser mapping system calculates one or more of: athree-dimensional topographical map of the scene, a dimension of one ormore objects within the scene, or a distance.
 45. The system of claim44, wherein the controller is further configured to generate an overlayimage frame comprising: a color image frame sensed by the image sensorin response to the emitter pulsing a visible wavelength ofelectromagnetic radiation; data indicating the location of the tissuestructure within the scene as determined by the correspondingfluorescence system; and data comprising one or more of thethree-dimensional topographical map of the scene, the dimension of theone or more objects within the scene, or the distance as determined bythe corresponding laser mapping system.
 46. The system of claim 31,wherein the multispectral source comprises a plurality of independentmultispectral sources each configured to emit a different partition ofelectromagnetic radiation, and wherein the image sensor senses aplurality of independent multispectral frames, and wherein each of theplurality of independent multispectral frames is sensed in response toan emission by one or more of the plurality of independent multispectralsources.
 47. The system of claim 46, further comprising a controllerconfigured to provide the plurality of independent multispectral framesto a corresponding multispectral system configured to determine anidentity of a tissue structure within a scene based on data from one ormore of the plurality of independent multispectral frames.
 48. Thesystem of claim 47, wherein the corresponding multispectral systemdetermines whether pixel data in each of the plurality of multispectralframes exceeds or falls below a threshold.
 49. The system of claim 48,wherein the controller is further configured to provide a laser mappingframe to a corresponding laser mapping system, wherein the laser mappingframe is sensed by the image sensor in response to an emission by thelaser mapping source, and wherein the corresponding laser mapping systemcalculates one or more of a three-dimensional topographical map or adimension of the identified tissue structure based at least in part onthe laser mapping frame.
 50. The system of claim 31, further comprisinga filter for filtering the fluorescence excitation wavelength to preventthe image sensor from being irradiated by the fluorescence excitationwavelength, and wherein the image sensor senses a fluorescence frame inresponse to an emission by the fluorescence source, and wherein theimage sensor senses a fluorescence relaxation wavelength to generate thefluorescence frame.